US7763198B2 - Method for retaining a vascular stent on a catheter - Google Patents

Method for retaining a vascular stent on a catheter Download PDF

Info

Publication number
US7763198B2
US7763198B2 US11453747 US45374706A US7763198B2 US 7763198 B2 US7763198 B2 US 7763198B2 US 11453747 US11453747 US 11453747 US 45374706 A US45374706 A US 45374706A US 7763198 B2 US7763198 B2 US 7763198B2
Authority
US
Grant status
Grant
Patent type
Prior art keywords
stent
balloon
mold
method
balloon catheter
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active, expires
Application number
US11453747
Other versions
US20070204455A1 (en )
Inventor
Boyd V. Knott
Sean McNiven
Jeremy Stigall
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Abbott Cardiovascular Systems Inc
Original Assignee
Abbott Cardiovascular Systems Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Grant date
Family has litigation

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/95Instruments specially adapted for placement or removal of stents or stent-grafts
    • A61F2/958Inflatable balloons for placing stents or stent-grafts
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/95Instruments specially adapted for placement or removal of stents or stent-grafts
    • A61F2002/9522Means for mounting a stent onto the placement instrument
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0058Additional features; Implant or prostheses properties not otherwise provided for
    • A61F2250/0067Means for introducing or releasing pharmaceutical products into the body
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T29/00Metal working
    • Y10T29/49Method of mechanical manufacture
    • Y10T29/49826Assembling or joining
    • Y10T29/49908Joining by deforming
    • Y10T29/49909Securing cup or tube between axially extending concentric annuli
    • Y10T29/49913Securing cup or tube between axially extending concentric annuli by constricting outer annulus

Abstract

A method of securely mounting a stent on a balloon of a balloon catheter. The method generally includes crimping a stent on a balloon of a balloon catheter, and positioning the balloon with the drug delivery stent thereon within a polished bore of a mold formed at least in part of a metallic material. The balloon is pressurized and heated within the mold as the mold radially restrains the stent from expanding. The stent is re-crimped on the balloon after removal from the mold to increase retention of the stent on the balloon.

Description

CROSS-REFERENCES TO RELATED APPLICATIONS

This application claims priority to and is a continuation-in-part of U.S. Ser. No. 11/105,085 filed Apr. 12, 2005 now U.S. Pat. No. 7,563,400 and entitled “METHOD OF STENT MOUNTING TO FORM A BALLOON CATHETER HAVING IMPROVED RETENTION OF A DRUG DELIVERY STENT,” the entirety of which is incorporated herein by reference.

BACKGROUND OF THE INVENTION

This invention relates generally to catheters and stents, and particularly to methods for retention of stents on intravascular stent delivery catheters.

In percutaneous transluminal coronary angioplasty (PTCA) procedures a guiding catheter is advanced in the patient's vasculature until the distal tip of the guiding catheter is seated in the ostium of a desired coronary artery. A guidewire is first advanced out of the distal end of the guiding catheter into the patient's coronary artery until the distal end of the guidewire crosses a lesion to be dilated. A dilatation catheter, having an inflatable balloon on the distal portion thereof, is advanced into the patient's coronary anatomy over the previously introduced guidewire until the balloon of the dilatation catheter is properly positioned across the lesion. Once properly positioned, the dilatation balloon is inflated with inflation fluid one or more times to a predetermined size at relatively high pressures so that the stenosis is compressed against the arterial wall and the wall expanded to open up the vascular passageway. Generally, the inflated diameter of the balloon is approximately the same diameter as the native diameter of the body lumen being dilated so as to complete the dilatation but not overexpand the artery wall. After the balloon is finally deflated, blood flow resumes through the dilated artery and the dilatation catheter and the guidewire can be removed therefrom.

In such angioplasty procedures, there may be restenosis of the artery, i.e. reformation of the arterial blockage, which necessitates either another angioplasty procedure, or some other method of repairing or strengthening the dilated area. To reduce the restenosis rate of angioplasty alone and to strengthen the dilated area, physicians now normally implant an intravascular prosthesis, generally called a stent, inside the artery at the site of the lesion. Stents may also be used to repair vessels having an intimal flap or dissection or to generally strengthen a weakened section of a vessel or to maintain its patency. Stents are usually delivered to a desired location within a coronary artery in a contracted condition on a balloon of a catheter which is similar in many respects to a balloon angioplasty catheter, and expanded within the patient's artery to a larger diameter by expansion of the balloon. The balloon is deflated to remove the catheter and the stent left in place within the artery at the site of the dilated lesion. See for example, U.S. Pat. No. 5,507,768 (Lau et al.) and U.S. Pat. No. 5,458,615 (Klemm et al.), which are incorporated herein by reference.

The stent must be securely yet releasably mounted on the catheter balloon for delivery and deployment at the desired location in a patient's body lumen. If the stent becomes dislodged from or moved relative to the balloon during delivery, the system will not correctly implant the stent in the body lumen. However, the stent can't be so strongly fixed to the balloon that it inhibits expansion of the balloon and/or release of the stent once the balloon is positioned at the desired location. One difficulty has been retention of stents, including stents having a drug delivery layer. The mounting process used to secure the drug delivery stent to the balloon must not damage the stent. Furthermore, the stent retention process must not damage a stent including a drug or the matrix material containing the drug. It would be a significant advance to provide a catheter balloon having improved retention of a stent, for example, a drug delivery stent, and without inhibiting balloon or stent function. The present invention satisfies these and other needs.

SUMMARY OF THE INVENTION

One aspect of the present invention is directed to a method of mounting a stent on a stent delivery balloon catheter. Yet another aspect of the invention is a method of mounting a drug delivery stent on a balloon, and a stent delivery balloon catheter produced therefrom. Still another aspect of the invention is a method that securely mounts a drug delivery stent on a balloon catheter without damaging the drug delivery layer of the stent.

In one aspect of the invention, the method generally comprises positioning a stent, for example, a drug delivery stent, on a balloon of a balloon catheter, and positioning the balloon with the stent thereon within a polished bore of a mold formed at least in part of a metallic material. In yet a further aspect of the invention, the stent is a drug delivery stent, and the balloon is pressurized and heated within the mold to mount the stent on the balloon, without damaging the drug delivery layer of the stent. The mold radially restrains the stent from expanding when the balloon is pressurized therein, so that the balloon can be forced into the gaps in the stent wall using inflation pressures higher than those which normally cause radial expansion of the stent. The bore of the mold is defined by a polished inner surface with a polished finish which is sufficiently smooth so that contact and relative movement between the stent and polished inner surface of the mold does not roughen or otherwise damage or create a texture on the drug delivery layer of the stent. As a result, the release rate of the drug from the drug delivery layer is substantially equal to the release rate prior to stent mounting. In another aspect of the invention, the smooth surface of the drug delivery layer, which is free of roughness and irregularities caused by the stent mounting, provides the drug delivery layer with a uniform thickness which is within the normal variance produced by the method used to form the drug delivery layer. Additionally, the inner surface of the mold does not cause the drug delivery layer to transfer drug to the inner surface of the mold during the stent mounting, so that the amount of drug present in the drug delivery layer is substantially equal to the amount prior to stent mounting.

In yet another aspect of the invention, the drug delivery layer of the stent is a coating applied to a surface of the radially expandable tubular body of the stent. However, a variety of suitable configurations may be used as are well known in the art, including embodiments in which the tubular body of the stent is itself formed of a drug delivery matrix, or the drug delivery layer is a tubular sleeve on a surface of the body of the stent. Additionally, the drug delivery layer should be understood to broadly refer to configurations which deliver or present one or more drugs by any of a variety of suitable mechanisms including eluting the drug from the layer, bioabsorption of a drug delivery matrix, and the like. The stent may be biostable and/or bioabsorable. The terminology “drug” as used herein should be understood to refer to a variety of therapeutic and diagnostic agents. In a further aspect of the invention, the drug is intended to prevent or inhibit restenosis.

The balloon is heated by heating the mold using a heat transfer medium which provides temperature control to the mold with a tolerance of about ±1 degree to about ±2 degrees Fahrenheit (F.)). In still another aspect of the invention, heating the mold comprises submerging the mold in a liquid bath, or contacting the surface of the mold with a conductive heating element. As a result, the heat transfer medium heats the mold primarily by conduction, and provides for finer temperature control and quicker heating than is provided by heating methods which heat primarily by convection (e.g., heating with hot air). In contrast, heating with hot air provides a heating tolerance of about ±10 degrees. In a presently preferred embodiment, the heat transfer medium is a conductive heating element such as a platen (e.g., a heated flat metal plate) configured to provide uniform heating of the balloon within the mold when the platen is in contact with the mold. Thus, the temperature is uniform (i.e., within about ±2 degrees F.) along the length of the section of the mold exposed to the heating medium, and the temperature at any given point of the heated length remains constant (i.e., within ±2 degrees F.) during the heating. With the metal platen pressed against an outer surface of the mold, the platen heats purely by conduction (unlike a hot circulating heating medium which heats by both conduction and convention), and provides for finer temperature control at the surface of the mold than a hot liquid bath or hot air. The temperature control provided by the heat transfer medium prevents the drug from being exposed to an elevated temperature which is above the thermal limit of the drug, while allowing the balloon to be quickly heated to a sufficiently high temperature to soften the balloon material during stent mounting.

In still another aspect of the invention, in which the heat transfer medium is a hot liquid bath, the mold is configured to seal the bore of the mold with the catheter therein, so that the mold is submerged without liquid or humidity from the liquid bath contacting the drug delivery stent in the mold. As a result, the drug delivery layer is not dissolved or otherwise damaged by exposure when the mold is submerged in the liquid bath.

The metallic material of the mold allows the mold to be machined with tight dimensional tolerances, to provide an accurate and uniform bore diameter. Additionally, the metallic material of the mold provides sufficient strength, even at elevated temperature, so that the mold radially restrains the stent during the stent mounting procedure without the diameter of the mold bore increasing. Thus, unlike a radial restraining member which expands somewhat during pressurization of the balloon therein, the mold of the invention controls the outer diameter of the mounted stent, so that the profile of the mounted stent is not disadvantageously increased during the stent mounting. The profile of the mounted stent can impact the ability of the stent delivery balloon catheter to advance and cross tight lesions in the patient's vasculature.

The mold is a split-mold having hinged halves. The mold halves swing open and close at the hinge so that the balloon with the stent thereon can be introduced or removed from the mold without damaging the drug delivery layer of the stent. The mold therefore prevents or inhibits the damage to the drug delivery layer which can otherwise occur with tubular radial restraining members which don't open up for introduction of the balloon catheter and which must be cut off the balloon catheter after the stent mounting. Additionally, the mold of the invention is reusable, and provides for accurate, uniform heating which does not vary with each subsequent use.

In another aspect of the invention, the mold body defining the entire length of the bore and outer surface of the mold is formed of metal. As a result, the metal mold substantially uniformly heats the entire length of the balloon within the bore of the mold. However, in yet another aspect of the invention, the mold has a body with a heat conducting metallic section and an insulating non-metal section, so that heating the mold selectively heats sections of the balloon within the bore of the mold. The insulating section of the mold insulates the drug-delivery stent during the stent mounting procedure, so that the drug delivery stent is heated to a lower temperature than the inflatable sections of the balloon at either end of the stent. As a result, the balloon is sufficiently heated for the stent mounting procedure without exposing the drug-delivery stent to a disadvantageously high temperature (e.g., a temperature above the thermal limit of the drug).

A stent delivery balloon catheter of the invention generally comprises an elongated shaft having an inflation lumen and a guidewire lumen, a balloon on a distal shaft section having an interior in fluid communication with the inflation lumen, and a stent releasably mounted on the balloon for delivery and deployment within a patient's body lumen. The stent typically comprises an open-walled body of stent struts with gaps between adjacent struts. The balloon typically has a folded noninflated configuration with wings wrapped around the circumference of the balloon. In alternative embodiments, the balloon is a wingless balloon which expands by stretching from a wingless noninflated configuration.

Yet another aspect of the invention is directed to a mold having a stepped inner diameter comprising enlarged inner diameter sections on either end of a middle section. During stent mounting, the stepped inner diameter forms one or more external shoulders in the balloon. The balloon shoulders are located adjacent the end(s) of the stent, to prevent or inhibit the stent from moving longitudinally relative the balloon during delivery and deployment of the stent. The balloon external shoulders have an outer diameter larger than the outer diameter of the unexpanded stent, and thus provide a barrier that the stent would have to overcome in order to move longitudinally relative to the balloon. The external shoulders are thus molded into the balloon material during stent mounting and are not the result of material added to the shaft or balloon. As a result, the shoulders are formed without affecting the stiffness transitions of the catheter.

Another aspect of the invention is directed to a method of mounting a stent on a stent delivery balloon catheter using the mold having a stepped inner diameter. The method generally comprises introducing inflation media into the interior of the balloon, and heating the balloon, to radially expand the balloon with the stent restrained from radially expanding by a mold around an outer surface of the stent, so that the balloon expands into the stent gaps to embed the stent in an outer surface of the balloon, to thereby mount the stent on the balloon, wherein the mold has a stepped inner diameter so that expanding the balloon forms at least one shoulder in the balloon adjacent an end of the stent with an outer diameter greater than an outer diameter of the mounted stent in an unexpanded configuration.

In one aspect, the invention provides a method of mounting a drug delivery stent on a catheter balloon which provides a low profile mounted stent, and which securely and consistently mounts the stent on the balloon for delivery and deployment within a patient's body lumen without damaging the drug delivery layer of the stent. The metallic mold, heated primarily by conduction during stent mounting, allows temperature control to the mold sufficient to prevent heat damage of the drug delivery layer. The mold is heated with a method configured to avoid the nonuniformity and irreproducibility of convective heat transfer. Additionally, the mold is configured to prevent or reduce roughening or otherwise mechanically damaging the drug delivery layer, so that the drug delivery layer release rate and drug amount are not disadvantageously effected by the stent mounting procedure of the invention. In still another aspect of the invention, the mold has heat conducting portions and insulating portions, and heating the mold selectively heats sections of the balloon and stent within the bore of the mold. In yet another aspect of the invention directed to a mold with a stepped inner diameter, the mold produces one or more shoulders in the balloon which enhance stent retention on the balloon.

In yet one further aspect of the present invention, the method may further including re-crimping the catheter assembly after removal from the split mold. Re-crimping may be done by hand, hand tool, or using a crimping tool or machine. In one aspect of the invention, the re-crimping is performed using an MSI crimper available from Machine Solutions Incorporated, Flagstaff Ariz. In yet another aspect of the invention, the re-crimping may be performed using a stent press machine available from Advanced Cardiovascular Systems, Inc., Santa Clara, Calif.

In still another aspect of the invention, during the re-crimping process, the balloons may be pressurized and heated to increase the protrusion of balloon material into the openings in the stent pattern, thereby further increasing stent retention on the balloons. In one aspect of the invention, the balloon may be pressurized in the range of 10 to 300 pounds per square inch (psi) (7 to 207 newtons per square centimeter). In one aspect of the invention, the balloon and the mounted stent are heated to the range of about 100 degrees to 250 degrees Fahrenheit (38 to 121 degrees Celsius) during re-crimping. In yet another aspect of the invention, the mounted stent is heated to about 130 degrees Fahrenheit (54 degrees Celsius) during re-crimping. In another aspect of the invention, the balloon may be pressurized to about 70 psi (48 newtons per sq. centimeter). In yet a further aspect of the invention, the balloon may be pressurized to more or less pressure.

Re-crimping may increase the retention of the stent to the balloon, particularly if the catheter assembly is to be gas sterilized with ethylene oxide (EtO). In one aspect of the invention, the method includes a first stage of crimping the stent on the balloon catheter assembly before sterilization. The crimping before sterilization may be performed using any presently available crimping machine or crimping assembly. A crimping assembly may also be referred to sometimes as a crimping press. In yet a further aspect of the invention, after the first stage of crimping, the balloon is pressurized and heated within the mold to further mount the stent on the balloon. In still another aspect of the invention, a second crimping of the stent on the balloon catheter assembly is performed after removal from the mold, hereinafter also referred to as re-crimping.

In one aspect of the present invention, the method includes re-crimping the catheter assembly after removal from a split mold process. During the split mold process, pressure is applied to the balloon, and heat is applied to the balloon-stent assembly. It is after the split mold process that the balloon is likely to pull away from the stent, especially after EtO sterilization. Re-crimping is advantageous in securing the stent onto the balloon after the split mold process and when sterilization is accomplished by EtO sterilization. Re-crimping may also be advantageous in securing the stent onto the balloon after the split mold process when other sterilization methods are used.

In accordance with certain aspects of the present invention there may be provided a stent crimping assembly as disclosed in U.S. Pat. No. 6,840,081 filed Nov. 18, 2002 and entitled “ASSEMBLY FOR CRIMPING AN INTRALUMINAL DEVICE OR MEASURING THE RADIAL STRENGTH OF THE INTRALUMINAL DEVICE AND METHOD OF USE” which issued Jan. 11, 2005, the entire contents of which are incorporated herein by reference.

In further accordance with the present invention, there may be provided a stent crimping assembly as disclosed in U.S. Ser. No. 10/330,016 filed Dec. 26, 2002 and entitled “ASSEMBLY FOR CRIMPING AN INTRALUMINAL DEVICE AND METHOD OF USE” the entire contents of which are incorporated herein by reference.

One aspect of the present invention is a method of mounting a stent on a balloon catheter, including positioning the stent on a balloon of the balloon catheter and applying a first radially compressive force on an outer surface of the stent, thereby decreasing the outer diameter of the stent on the balloon catheter. The method also includes pressurizing and heating the balloon while restricting radial expansion of the outer surface of the stent. Yet a further aspect of the invention includes applying a second radially compressive force on the outer surface of the stent.

At least one aspect of the invention is a method of mounting a stent on a balloon catheter. The method includes positioning a stent on a balloon catheter, the balloon catheter having an elongated shaft with an inflation lumen and a guidewire lumen and an inflatable balloon on a distal shaft section with an interior in fluid communication with the inflation lumen. The stent has an open-walled body of stent struts with gaps between adjacent stent struts. The method further includes applying a first radially compressive force on an outer surface of the stent and thereby decreasing the outer diameter of the stent on the balloon catheter. In yet another aspect, the invention includes heating the balloon and introducing inflation media into the interior of the balloon to radially expand the balloon with the stent restrained from radially expanding, so that the balloon expands into the stent gaps to embed the stent in an outer surface of the balloon, and thereby mount the stent on the balloon. In at least one aspect of the invention, the stent is restrained from radially expanding by a mold. In yet one other aspect of the invention, the method includes removing the inflation media from the balloon interior and applying a second radially compressive force on an outer surface of the stent. In at least another aspect of the invention, one factor in increased retention of the stent on the balloon is that the second radially compressive force decreases the outer diameter of the stent on the balloon catheter.

Still another aspect of the invention is a method of increasing retention of an intravascular device on a balloon catheter, including a first stage of crimping the intravascular device onto a balloon of the balloon catheter, a second stage of heating and pressurizing the balloon, and a third stage of re-crimping the intravascular device onto the balloon of the balloon catheter.

Other features and advantages of the invention will become more apparent from the following detailed description of preferred embodiments of the invention, when taken in conjunction with the accompanying exemplary drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is an isometric view of a mold useful in a method which embodies features of the invention, in which a drug delivery stent is mounted onto a balloon catheter.

FIG. 2 is an isometric view of the mold of FIG. 1 in a closed configuration, illustrating a distal section of a balloon catheter within the mold.

FIG. 3 is a longitudinal cross sectional view illustrating the mold of FIG. 2 with heating platens on an outer surface of the mold during a method of mounting a drug delivery stent on the balloon of the balloon catheter.

FIG. 4 is a diagrammatic transverse cross section of the assembly of FIG. 3, taken along line 4-4.

FIG. 5 is a perspective view of the mold of FIG. 3 in an open configuration allowing for removal from the mold of the stent delivery balloon catheter having the drug delivery stent mounted on the balloon.

FIG. 6 is an elevational view of the stent delivery balloon catheter of FIG. 5 after being removed from the mold.

FIG. 7 is a transverse cross sectional view of the stent delivery balloon catheter of FIG. 6, taken along line 7-7.

FIG. 8 illustrates a stent delivery balloon catheter embodying features of the invention, in which the balloon forms shoulders adjacent the ends of the stent.

FIG. 9 illustrates a mold useful in a method of mounting a stent on a balloon catheter, having a stepped inner diameter, to form the shoulders in the balloon.

FIG. 10 illustrates a longitudinal cross sectional view of an alternative embodiment of a stepped inner diameter mold useful in a method of mounting a stent on a balloon catheter, in which end portions of the middle section of the mold have a smaller inner diameter than the portion of middle section therebetween.

FIG. 11 is an isometric view of an alternative mold useful in a method embodying features of the invention, having an insulating non-metal body portion and a metal body portion.

FIG. 12 illustrates a longitudinal cross sectional view of the mold bottom half of FIG. 11, taken along line 12-12.

FIG. 13 is an isometric view of an alternative partially insulating mold useful in a method embodying features of the invention, having a metallic body with insulating non-metal inserts.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

FIG. 1 illustrates a metal mold 10 useful in a method of mounting a drug delivery stent on a balloon catheter, embodying features of the invention. Mold 10 generally comprises a split metal body 11 with a bottom half, a top half, and a polished bore 12 configured to receive a balloon catheter therein. In the embodiment illustrated in FIG. 1, the top and bottom halves of the mold are joined by a hinge, and the mold is illustrated in an open configuration. FIG. 2 illustrates the mold in a closed configuration with a distal section of a balloon catheter 20 in position within the mold.

FIG. 3 illustrates the mold 10 with the distal section of the balloon catheter 20 therein, partially in longitudinal cross section, during a method of mounting a drug delivery stent on the balloon catheter 20. The balloon catheter 20 has an elongated shaft 21 with a balloon 22 on a distal section thereof and a drug delivery stent 23 on the balloon. The balloon 22, with the drug delivery stent 23 thereon, are completely contained within the polished bore 12 of the mold 10. FIG. 4 illustrates a diagrammatic transverse cross sectional view of FIG. 3, taken along line 4-4.

A method of releasably mounting the drug delivery stent 23 on the balloon 22 generally comprises positioning the drug delivery stent 23 on the uninflated balloon 22 of the balloon catheter 20. The stent is typically mechanically crimped (i.e., radially collapsed) down onto the balloon 22. A distal end section of the catheter 20 is placed within the mold, to position the balloon with the crimped stent 23 thereon within the polished bore 12 of the mold 10. The hinged halves of the mold are closed together, and the balloon 22 is pressurized by introducing inflation fluid into the interior of the balloon 22 and heated to an elevated temperature. In a presently preferred embodiment, the balloon is pressurized and then heated in the pressurized condition. In an alternative embodiment, the balloon is simultaneously pressurized and heated. The balloon material at the elevated temperature and pressure is forced into the gaps in the wall of the stent 23, to embed the stent within the outer surface of the balloon. FIG. 3 illustrates the balloon in the pressurized and heated state, with the stent contacting the polished inner surface of the bore of the mold to radially restrain the stent from radially expanding. In one embodiment, the balloon is pressurized to a relatively high pressure of about 15 to about 23 atm, more specifically about 19 to about 21 atm. The balloon is then cooled in the mold prior to depressurization of the balloon, and the cooled balloon depressurized, and the balloon catheter removed from the mold with the stent mounted on the balloon. FIG. 5 illustrates the mold 10 in an open configuration facilitating removal of the balloon catheter 20 therefrom after the stent 23 is mounted onto the balloon 22.

The mold bore 12 is defined by a polished inner surface of the top and bottom halves of the mold. In a presently preferred embodiment, the polished inner surface has a polish finish of about 0.4 microns or less. The bore is polished by techniques known in the art, such as honing. The polished inner surface contacts the stent, and provides a smooth surface which prevents or inhibits roughening the surface of the drug delivery stent 23 during the stent mounting procedure.

In the embodiment illustrated in FIGS. 1-5, the diameter of the bore 12 is the same along the entire length of the mold 10. The bore 12 is preferably formed by machining so that the diameter of the bore is highly accurate and uniform (i.e., the diameter varies by no more than ±0.025 mm along the length of the mold, and multiple molds can be made having the same dimensions). The bore 12 is preferably machined within the block which forms the body of the mold 10, with the two halves of the mold 10 in place together during the machining. As a result, the top and bottom sections of the bore 12 perfectly and repeatably mate together when the two halves of the mold 10 are closed together. In a presently preferred embodiment, the diameter of the mold bore 12 is slightly larger than the outer diameter of the crimped stent 23 on the balloon 22. As a result, the diameter of the mold bore 12 is large enough to avoid scuffing/damaging the drug delivery layer of the stent 23 when the balloon 22 and stent 23 crimped thereon are placed within the bore 12. In an alternative embodiment, the diameter of the mold bore 12 is equal to the diameter of the crimped stent 23 on the balloon 22, so that the stent does not radially expand during the stent mounting. Each half of the mold 10 preferably has relatively thin walls, e.g., with a wall thickness of not greater than about 0.25 to about 0.5 mm, at its thinnest along a midline of the bore 12 of the mold (i.e., the wall thickness from the outer surface of the mold half to the bore), to provide fast heating and cooling within the bore 12 of the mold 10.

In accordance with the invention, the balloon 22 is heated by heating the mold 10 with a heat transfer medium which provides very accurate temperature control to the mold 10. In the embodiment illustrated in FIG. 3, the heat transfer medium is a conductive heating element member in the form of metal platens 30. The metal platens 30 have a heating element (not shown) such as a resistive heater which heats the metal of the platens, and an inner surface typically configured to correspond to the outer surface of the mold 10. In the illustrated embodiment, the inner surface of the platens 30 and the outer surface of the mold 10 are flat, although, in alternative embodiments (not shown), the surfaces have irregular mating surfaces designed to increase the surface area thereof. The temperature at the surface of the platens 30 is very accurately controllable, so that, with the surface of the metal platens 30 pressed against the outer surface of the mold 10, the temperature of the mold can be very accurately controlled (i.e., with a tolerance which is not larger than about ±2 degrees F., more preferably with a tolerance of about ±1 degree F.).

With the balloon catheter 20 in position within the bore 12 of the mold 10, the mold 10 is slid into the space between the metal platens 30, and the metal platens 30 brought into contact with the outer surface of the top and bottom halves of the mold, to thereby heat the mold 10. The mold 10 is heated to an elevated temperature sufficient to soften the balloon 22 but lower than the thermal limit of the drug of the drug delivery stent 23. In a presently preferred embodiment, the temperature within the mold 10 is below a temperature which would cause the drug delivery layer of the stent 23 to flow. However, in an alternative embodiment in which the drug delivery layer of stent 23 is heated and flows somewhat at the elevated temperature, the smooth inner surface of the polished bore 12 causes the drug delivery layer to remain uniform in thickness without a roughened or irregular exterior. In one embodiment, the mold 10 is heated to a temperature of about 160° F. to about 190° F., with the balloon catheter 20 therein during the stent mounting procedure, to soften a balloon formed of polymeric material.

The metal platens 30 have a relatively high thermal conductivity, higher than that of air at least in the temperature range of interest, providing a relatively fast rate of heating. In one embodiment, the mold 10 is in contact with the heating platens 30 for not greater than about 120 seconds, and more specifically for about 60 to about 120 seconds during the stent mounting procedure. In contrast, hot air would take significantly longer, and for example not less than about 120 seconds (e.g., on the order of about 120 to about 240 seconds), to heat the mold to the desired temperature. The platens 30 and mold 10 are configured to provide a fast heating rate in combination with fine control of the elevated temperature, for improved mounting of the drug delivery stent 23 without damage to the drug delivery layer.

The platens 30 have a length which, in one embodiment, is at least as long as the stent 23, and the platens are brought into contact with a length of the mold 10 corresponding to the location of the drug delivery stent 23 therein. In the embodiment illustrated in FIG. 3, the platens are longer than the stent but shorter than the balloon, although a variety of suitable configurations can be used including platens having a length which is shorter than the stent, or platens having a length equal to the length of the mold 10. In a presently preferred embodiment, the platens have a length which is at least as long as, or substantially equal to, the length of the inflatable section of the balloon (i.e., the working length and tapered sections). Although discussed primarily in terms of the embodiment in which the mold is heated with platens 30, alternative heating mediums that heat primarily by conduction can be used including a hot liquid bath. In the embodiment using a hot liquid bath (not shown), the mold 10 has seals (not shown) at either end of the mold which seal around the balloon catheter 20 to prevent the liquid or humidity of the hot liquid bath from contacting the drug delivery stent 23 within the mold 10 when the mold is submerged within the bath.

FIG. 6 illustrates the stent delivery balloon catheter 20 embodying features of the invention, after removal from the mold 10 with the drug delivery stent 23 mounted on the balloon 22. In the illustrated embodiment, the catheter shaft 21 comprises an outer tubular member 24 defining an inflation lumen 25 therein, and an inner tubular member 26 defining a guidewire lumen 27 therein configured to slidingly receive a guidewire 28. Specifically, in the illustrated embodiment, the coaxial relationship between outer tubular member 24 and inner tubular member 26 defines annular inflation lumen 25. In the embodiment illustrated in FIG. 6, the guidewire lumen 27 extends to the proximal end of the catheter. Inflatable balloon 22 has a proximal skirt section sealingly secured to the distal end of outer tubular member 24 and a distal skirt section sealingly secured to the distal end of inner tubular member 26, so that the balloon interior is in fluid communication with inflation lumen 25. An adapter 29 at the proximal end of catheter shaft 21 is configured to provide access to guidewire lumen 27, and to direct inflation fluid through the arm into inflation lumen 25. As best shown in FIG. 7 illustrating a transverse cross section of the balloon catheter of FIG. 6, taken along line 7-7, the stent gaps are partially filled by the balloon material so that the balloon material contacts and partially encapsulates the side surfaces of the stent struts, to securely mount the stent on the balloon. In an alternative embodiment (not shown), the balloon material completely fills the stent gaps to fully encapsulate the side surfaces of the stent struts. In the embodiment illustrated in FIGS. 6 and 7 the portions of the balloon which protrude between the stent struts have an outer surface flush with the outer surface of the stent.

FIG. 6 illustrates the balloon 22, in a folded configuration with wings wrapped around the circumference of the balloon prior to complete inflation of the balloon. The balloon 22 typically has two or more, and most preferably three wings in the noninflated configuration, which unwrap during inflation of the balloon 22. For ease of illustration, a substantial gap is illustrated between the inner surface of the inflatable balloon interior and the shaft inner tubular member 26 in FIGS. 6 and 7, although it should be understood that the noninflated balloon is typically collapsed down around to inner tubular member in the noninflated configuration. The balloon expands to a generally cylindrical inflated configuration with a central working length inflated section, a proximal inflated conical tapered section proximal to the stent (and distal to the proximal skirt section), and a distal inflated conical tapered section distal to the stent (and proximal to the distal skirt section). FIG. 6 illustrates the stent 23 mounted on the central, working length section of the balloon 22, prior to complete expansion. The distal end of catheter 20 may be advanced to a desired region of the patient's body lumen in a conventional manner with the balloon in the noninflated configuration, and the balloon 22 inflated by directing inflation fluid into the balloon interior to expand the stent 23. The balloon is then deflated, leaving the drug delivery stent 23 implanted in the body lumen.

The stent 23 generally comprises an open-walled tubular body of interconnected, spaced-apart stent struts 31 with gaps 32 between adjacent stent struts. In the illustrated embodiment, the stent struts 31 form rings which have a serpentine wave pattern of opposed turns and which are longitudinally spaced apart and connected by links 33. However, the stent 23 can have a variety of suitable configurations as are conventionally known. The tubular body of the stent 23 is typically a biostable material such as a metal, although it can alternatively be formed of a bioabsorable material. In a presently preferred embodiment, the drug delivery layer is a coating (not shown) applied to the surface of the tubular body of the stent 23.

Although the embodiment illustrated in FIG. 6 is directed to embedding the drug delivery stent 23 in the outer surface of the layer of a single-layered balloon, it should be understood that the balloon can alternatively be formed of multiple layers or with an outer sleeve member, so that embedding the stent into the balloon embeds the stent in the outer surface of the outer most layer or outer sleeve of the balloon.

FIG. 8 illustrates an alternative embodiment of a stent delivery balloon catheter 40 embodying features of the invention, having an elongated shaft 41 and a balloon 42 on a distal shaft section with a proximal external shoulder 44 adjacent a proximal end of the stent 43 with an outer diameter larger than the outer diameter of the nonexpanded stent mounted on the balloon, and a distal external shoulder 45 adjacent a distal end of the stent 43 with an outer diameter larger than the outer diameter of the nonexpanded stent mounted on the balloon. Alternatively, the balloon can have only one of the proximal 44 or distal 45 external shoulders. For example, in one embodiment (not shown), the balloon has the distal external shoulder 45, and not the proximal external shoulder 44. The external shoulders 44, 45 are located along the proximal and distal inflatable sections of the balloon (e.g., along the sections of the balloon which inflate to form the proximal and distal conical tapered sections in the inflated configuration, at the junction between the inflatable conical tapered section of the balloon and the end of the working length section). The stent 43 is similar to drug delivery stent 23 discussed above in relation to the embodiment of FIG. 1.

In the illustrated embodiment, the balloon 42 comprises an inner layer 46 and an outer sleeve member 47 which defines the outer surface of the external shoulders 44, 45. The outer sleeve 47 is typically formed of a relatively low melting point elastomeric polymer. In the embodiment illustrated in FIG. 8, molding the external shoulders 44, 45 in the outer sleeve 47 of the balloon also forms shoulders in the balloon inner layer 46.

The balloon 42 is illustrated in a partially inflated configuration in FIG. 8 for ease of illustration, but it should be understood that the working length of the balloon is typically collapsed down to the shaft inner tubular member in the noninflated configuration for advancement within the patient's body lumen. In one embodiment, the balloon inflates to a cylindrical, fully inflated configuration (i.e., with no shoulders 44, 45 in the outer surface of the expanded balloon). The shoulders 44, 45 thus substantially disappear as the balloon expands, with the working length of the balloon expanding to define the maximum inflated diameter of the balloon, and the conical sections on either end of the working length section tapering away from the working length section to a smaller outer diameter in the inflated configuration.

In a method of mounting the stent 43 on the balloon catheter 40 to form the stent delivery system of FIG. 8, the radial restraining mold 50 has a stepped inner diameter which forms the external shoulders 44, 45 in the balloon during the stent gripping. FIG. 9 illustrates balloon catheter 40 within a radial restraining mold 50 having an inner chamber 51 configured for receiving the balloon portion of the balloon catheter 40. The radial restraining mold 50, similar to the embodiment of FIG. 1, typically has a bottom half attached by hinges to a top half, which facilitates positioning the balloon portion of the catheter in the inner chamber 51 of the mold. The inner chamber 51 has enlarged inner diameter sections 52 and 53 on either end of a middle section 54. The balloon is illustrated with the outer sleeve 47 and stent 43 thereon, during pressurization of the balloon to mount the stent on the balloon. As set forth above, the mold 50 radially restrains the stent 43 as inflation media is introduced into the interior of the balloon and the mold is heated to heat the balloon, so that the balloon expands into the stent gaps and the external shoulders 44, 45 are formed in the balloon by the enlarged inner diameter sections 52, 53 of the mold 50. In the embodiment illustrated in FIG. 8, the inner surface of the balloon also has a stepped configuration at the shoulders. As a result, a gap exists between the inner surface of the balloon at the shoulders 44, 45 and the outer surface of the shaft (or the outer surface of a radiopaque marker (not shown) on the shaft if the radiopaque marker is located beyond the end of the stent) in the noninflated configuration. Although the embodiment illustrated in FIGS. 8 and 9 has the outer sleeve 47 on the balloon inner layer 46, it should be understood that in an alternative embodiment (not shown) the outer sleeve 47 is omitted. The method fully or partially embeds the stent 43 in the balloon 42 depending on the balloon material and stent mounting method conditions.

FIG. 10 illustrates a longitudinal cross sectional view of an alternative radial restraining mold 60 with a stepped inner diameter, in which end portions 65, 66 of the middle section 64 of the mold have a smaller inner diameter than the portion of middle section 64 therebetween. The reduced inner diameter end portions 65, 66, cause the ends of the stent 30 to further embed down into the balloon during the stent mounting. Embedding the ends of the stent to a greater degree than a central section of the stent improves stent retention and advanceability of the system.

In a presently preferred embodiment, the mold 10/50/60 is formed of metal, so that the metallic body of the mold defines the entire length of the bore that receives the balloon, and defines an outer surface of the mold. The metallic body substantially uniformly heats the entire length of the balloon within the mold. In an alternative embodiment, the mold selectively heats sections of the balloon within the bore of the mold (i.e., the mold has sections which differentially conduct heat). For example, FIG. 11 illustrates an isometric view of an alternative radial restraining mold 70, having a body 71 formed of an insulating material such as a plastic with metal portions 72, which allows for selective heating of the balloon portion of a catheter. The metal portions 72 are heat conducting, and the insulating (e.g., plastic) body 71 is not heat conducting, or at least is substantially less heat conducting than the metal portions. For example, when a metal portion was heated to 163° F. (73° C.), the maximum temperature measured in the adjacent insulating plastic portion was 109° F. (43° C.). As a result, the balloon portion proximal and distal to the stent can be placed at the metal portions 72, with the balloon central working length section (having the stent thereon) located between the metal portions 72, so that the plastic of the mold body insulates the working length section of the balloon portion from the elevated temperatures used during the stent mounting.

Insulating at least the central working length section of the balloon portion from heat protects the drug delivery coating of the stent from damage during the stent mounting procedure. Depending on the length of the metal portions 72, the plastic body 71 typically also insulates the balloon skirt sections (secured to the shaft) from heat of the heat transfer medium during the stent mounting procedure.

In a presently preferred embodiment, the insulating material forming the mold body 71 is a plastic such as polyetheretherketone (PEEK), or a machinable polyimide such as Vespel, although non-plastic insulating materials can alternatively be used such as ceramics including Macor (a machinable glass ceramic).

FIG. 12 illustrates a longitudinal cross sectional view of the bottom half of the mold 70 of FIG. 11, taken along line 12-12. In a presently preferred embodiment, the metal portions 72 have, along at least a section thereof, a larger wall thickness (from the inner to the outer surface) than the adjacent sections of the plastic body 71 so that the metal portions 72 have at least a section which protrudes from the outer surface of the plastic body 71. The heating platens (discussed above in relation to the embodiment of FIG. 3) will therefore contact the protruding outer surface of the metal portions 72 without contacting the plastic body 71 during the stent mounting procedure. The air gap between the heating platens and the plastic body 71 sections will further reduce heat transfer to the drug delivery layer of a stent within the mold 70. In the illustrated embodiment, the plastic body 71, which together with the metal portions 72 defines the length of the bore receiving the balloon, is within an outer housing, typically formed of a metal, which surrounds the outer surfaces of the plastic body. The illustrated metal portions 72 have a section with a sufficiently large wall thickness such that the metal portions 72 protrude from the outer surface of the outer housing.

FIG. 13 illustrates an isometric view of an alternative embodiment of a selective heating mold 80 which embodies features of the invention, having a metallic body 81 with insulating plastic inserts 82. In the illustrated embodiment, three plastic inserts 82 are present, positioned at sections of the mold configured to receive the central working length section of balloon, and the skirt sections of the balloon secured to the shaft. The sections of the metallic body 81 of the mold located between the adjacent plastic inserts 82 are configured to receive the inflatable conical sections of the balloon (i.e., the balloon sections which extend between the central working length and the skirt sections of the balloon). The plastic inserts 82 preferably have a wall thickness which is less than the wall thickness of the metallic body 81. As a result, the metallic body 81 preferably defines the outer surface of the mold along the entire length thereof, and the metallic body 81 together with the plastic inserts 82 define sections of the bore of the mold. Alternatively, the wall thickness of the plastic inserts is equal to the wall thickness of the metallic body, so that the metallic body together with the plastic inserts define sections of the outer surface of the mold 80.

The dimensions of the stent delivery balloon catheter 20, 40 are determined largely by the size of the balloon and guidewire to be employed, the catheter type, and the size of the artery or other body lumen through which the catheter must pass or the size of the stent being delivered. Typically, the outer tubular member 24 has an outer diameter of about 0.025 to about 0.04 inch (0.064 to 0.10 cm), usually about 0.037 inch (0.094 cm), and the wall thickness of the outer tubular member 24 can vary from about 0.002 to about 0.008 inch (0.0051 to 0.02 cm), typically about 0.003 to 0.005 inch (0.0076 to 0.013 cm). The inner tubular member 26 typically has an inner diameter of about 0.01 to about 0.018 inch (0.025 to 0.046 cm), usually about 0.016 inch (0.04 cm), and a wall thickness of about 0.004 to about 0.008 inch (0.01 to 0.02 cm). The overall length of the catheter 20, 40 may range from about 100 to about 150 cm, and is typically about 143 cm. Preferably, balloon 22, 42 has a length of about 0.8 cm to about 6 cm, and an inflated working diameter of about 2 mm to about 10 mm.

Inner tubular member 26 and outer tubular member 24 can be formed by conventional techniques, for example by extruding and necking materials already found useful in intravascular catheters such a polyethylene, polyvinyl chloride, polyesters, polyamides, polyimides, polyurethanes, and composite materials. The various components may be joined using conventional bonding methods such as by fusion bonding or use of adhesives. Although the shaft is illustrated as having an inner and outer tubular member, a variety of suitable shaft configurations may be used including a dual lumen extruded shaft having a side-by-side lumens extruded therein. Similarly, although the embodiment illustrated in FIG. 6 is an over-the-wire type balloon catheter, the catheter of this invention may comprise a variety of intravascular catheters, such as rapid exchange type balloon catheters. Rapid exchange catheters generally comprise a shaft having a relatively short guidewire lumen extending from a guidewire distal port at the catheter distal end to a guidewire proximal port spaced a relatively short distance from the distal end of the catheter and a relatively large distance from the proximal end of the catheter.

The terms crimping and compressing as used herein are meant to be interchangeable and mean that the diameter of the stent is reduced to some degree. Typically, balloon-expandable stents 23 are known by persons having ordinary skill in the art to be “crimped” onto the balloon 22 portion of a catheter 20 while self-expanding stents are compressed onto a mandrel or sheath and then inserted into a catheter. The term re-crimping as used herein refers to a second radially compressive force on an outer surface of the stent following a first radially compressive force on an outer surface of the stent. The re-crimping may use the same crimping apparatus and/or method as the first crimping, or a different crimping apparatus and/or method. Both crimping and re-crimping include applying a radially compressive force on an outer surface of the stent and thereby decreasing the outer diameter of the stent on the balloon catheter. Re-crimping as used herein also refers to applying a radially compressive force on an outer surface of the stent after removal from the mold 10. The term pre-mounting as used herein refers to the stent being placed onto the catheter assembly and compressed before the stent mounted catheter is inserted into the crimping assembly for the first crimping process. In one embodiment, pre-mounting the stent onto the balloon of the catheter assembly includes compressing the stent onto the catheter with finger pressure before the stent mounted catheter is inserted into the crimping assembly.

Further, while reference is made herein to crimping or compressing “stents,” the invention can be used with any intraluminal device to reduce the diameter or measure radial strength. Thus, the invention is particularly useful with stents, grafts, tubular prostheses, embolic devices, embolic filters, and embolic retrieval devices.

The crimping processes referred to herein may be performed using the crimping assembly or apparatus referred to above or any other acceptable stent crimping assembly, apparatus, or method known in the art. A crimping assembly or apparatus may also be referred to sometimes as a crimping press. In one embodiment of the invention, a stent crimping assembly is used to crimp an expandable stent 23 onto the balloon 22 portion of a balloon catheter 20, however, the invention can be used with self-expanding stents as well. Examples of stent assemblies that may be used to crimp an expandable stent onto a balloon catheter include a stent crimping assembly as disclosed in U.S. Pat. No. 6,840,081 filed Nov. 18, 2002 and entitled “ASSEMBLY FOR CRIMPING AN INTRALUMINAL DEVICE OR MEASURING THE RADIAL STRENGTH OF THE INTRALUMINAL DEVICE AND METHOD OF USE” which issued Jan. 11, 2005, the entire contents of which are incorporated herein by reference and/or a stent crimping assembly as disclosed in U.S. Ser. No. 10/330,016 filed Dec. 26, 2002 and entitled “ASSEMBLY FOR CRIMPING AN INTRALUMINAL DEVICE AND METHOD OF USE” the entire contents of which are incorporated herein by reference.

In at least one embodiment, the invention includes a method of mounting a stent 23 on a balloon catheter 20. The stent is positioned on the balloon catheter by hand or apparatus. In at least one embodiment, the stent is pre-mounted onto the balloon 22 of the balloon catheter by a slight compressive pressure, for example, hand pressure. After positioning of the stent on the balloon, a first radially compressive force is applied on an outer surface of the stent, thereby decreasing the outer diameter of the stent on the balloon catheter. After applying of the first radially compressive force, the balloon is pressurized and heated while restricting radial expansion of the outer surface of the stent. In one embodiment, the pressurizing and heating of the balloon is done in a mold, for example, a split mold, configured to restrict the radial expansion of the outer surface of the stent. During the pressurizing and heating, outpouchings of the balloon may extend between undulations of the stent, further securing the stent on the balloon. However, the balloon may pull away from the stent somewhat as the balloon cools. The pulling away of the balloon from the stent may be exaggerated during EtO sterilization. Therefore, at least one embodiment includes applying a second radially compressive force on the outer surface of the stent. The second radially compressive force may decrease the outer diameter of the stent on the balloon catheter, wherein the stent is more securely mounted on the balloon. The first and/or second radially compressive forces may be applied by hand, by hand tool, or by machine, for example, a crimping maching. In at least one further embodiment, the assembly including the stent and balloon catheter may then be sterilized, for example, by EtO sterilization.

In at least one embodiment, the invention includes a method of increasing stent 23 retention on a balloon catheter 20. In one embodiment, the method includes a first stage of crimping the stent onto the balloon catheter before placing the balloon catheter with the stent mounted thereon in the mold 10, and a second stage of crimping of the stent onto the balloon catheter after the split mold process, described elsewhere herein, and before sterilization of the stent and balloon catheter assembly.

In a further embodiment, the invention is a method of increasing retention of an intravascular device on a balloon catheter, including a first stage of crimping the intravascular device onto a balloon of the balloon catheter, a second stage of heating and pressurizing the balloon, and a third stage of re-crimping the intravascular device onto the balloon of the balloon catheter.

In another embodiment, after the first stage of crimping, the stent 23 crimped on the balloon 22 is submitted to the split mold process described in greater detail above. After the first stage of crimping and the split mold process, the undulating rings of the stent indent into the balloon 22 resulting in out pouching or pillowing of the balloon into the openings between the undulations of the stent. In yet another embodiment, heating of the balloon and introducing inflation media into the interior of the balloon radially expands the balloon. The stent is restrained from radially expanding, for example, by the mold around an outer surface of the stent. As the balloon radially expands under heat, the balloon expands into the stent gaps to embed the stent in an outer surface of the balloon, thereby mounting the stent on the balloon.

However, a loss of stent retention may occur if sterilization of the balloon catheter 20 with the stent mounted thereon is performed directly after the split mold process. The loss of stent retention typically occurs with EtO (ethylene oxide) sterilization. One factor in the loss of stent retention may be that the balloon shrinks and pulls away from the stent during the sterilization process. Yet another factor in the loss of stent retention may be that the balloon shrinks and pulls away from the stent as it cools after the split mold process.

In one embodiment of the invention, the method may include applying at least one radially compressive force on the outer surface of the stent 23 that has been mounted on the balloon catheter 20 after removal from the mold 10. The mold may be a split mold. In one embodiment, the stent is pre-mounted on the balloon and positioned in the mold. After removal from the mold, a radially compressive force is applied on the outer surface of the stent before sterilization of the stent-balloon catheter assembly.

During the split mold process, pressure is applied to the balloon 22, and heat is applied to the balloon-stent assembly. It is after the split mold process that the balloon may pull away from the stent 23. Re-crimping is advantageous in securing the stent onto the balloon after removal from the mold 10. The advantage of re-crimping the stent onto the balloon catheter 20 is that the re-crimping may increase the retention of the stent to the balloon, particularly if the catheter assembly is to be gas sterilized with ethylene oxide (EtO). In at least one embodiment, the re-crimping is performed after the split mold process without another stage of crimping having been performed before the split mold process.

Re-crimping may be done by hand, using a crimping tool, a crimping machine, a crimping press, and/or a crimping assembly. In one preferred embodiment, the re-crimping is performed using an MSI crimper available from Machine Solutions Incorporated, Flagstaff Arizona. In one embodiment, the re-crimping may be performed using a stent press machine available from Advanced Cardiovascular Systems, Inc., Santa Clara, Calif.

In one embodiment, during the crimping and/or re-crimping process the balloon 22 may be pressurized and heated to increase the protrusion of balloon material into the openings in the stent 23 pattern, thereby further increasing stent retention on the balloon. In yet another embodiment of the invention, the balloon may be pressurized in the range of 10 to 300 pounds per square inch (psi) (7 to 207 newtons per square centimeter).

In at least one embodiment of the invention, the balloon 22 having the stent 23 mounted thereon is heated to the range of about 70 degrees to 250 degrees Fahrenheit (21 to 121 degrees Celsius) during re-crimping. In one embodiment the mounted stent is heated to about 130 degrees Fahrenheit (54 degrees Celsius) during re-crimping. In one embodiment, the balloon may be pressurized to about 70 psi (48 newtons per sq. centimeter). In other embodiments, the balloon may be pressurized to more or less pressure. In one embodiment, processing time during the re-crimping is in the range of one second to five minutes. In at least one embodiment, the processing time is approximately 10 seconds.

While the present invention is described herein in terms of certain preferred embodiments, those skilled in the art will recognize that various modifications and improvements may be made to the invention without departing from the scope thereof. For example, while discussed primarily in terms of a stent or a drug delivery stent, aspects of the invention may be useful with an alternative prosthesis or stent (e.g., a bare metal stent). Moreover, although individual features of one embodiment of the invention may be discussed herein or shown in the drawings of the one embodiment and not in other embodiments, it should be apparent that individual features of one embodiment may be combined with one or more features of another embodiment or features from a plurality of embodiments.

Claims (19)

1. A method of mounting a stent on a balloon catheter, comprising:
applying a drug coating to the stent;
positioning the stent on a balloon of the balloon catheter to create an assembly, wherein the stent includes an open-walled body formed from struts with gaps;
placing the stent and balloon catheter assembly into one half of complementary halves of a split mold, and closing the halves to enclose the assembly therein;
applying a first radially compressive force via the split mold on an outer surface of the stent, thereby decreasing the outer diameter of the stent on the balloon catheter;
pressurizing and heating the balloon while restricting radial expansion of the outer surface of the stent such that an outer surface of the expanding balloon embeds into the stent gaps; and
applying a second radially compressive force via the split mold on the outer surface of the stent.
2. The method of claim 1, wherein the pressurizing and heating of the balloon is performed in a mold configured to restrict the radial expansion of the outer surface of the stent.
3. The method of claim 2, wherein the stent is a drug delivery stent and mounting the stent on the balloon without damaging the drug delivery layer of the stent, includes heating the balloon by heating the mold by contacting a surface of the mold with a conductive heating element member which heats the mold purely by conduction and which provides temperature control to the mold with a tolerance of about ±1 degree to about ±2 degrees F.
4. The method of claim 2, wherein heating the mold includes submerging the mold in a liquid bath.
5. The method of claim 2, wherein heating the mold includes contacting a surface of the mold with a conductive heating element member.
6. The method of claim 1, wherein at least one of the radially compressive forces is applied by a crimping apparatus.
7. The method of claim 1, wherein at least one of the radially compressive forces is applied by a hand tool.
8. The method of claim 1, wherein at least one of the radially compressive forces is applied by hand.
9. A method of mounting a stent on a balloon catheter, comprising:
applying a drug coating to the stent;
positioning a stent on a balloon catheter to form an assembly, the balloon catheter having an elongated shaft with an inflation lumen and a guidewire lumen and an inflatable balloon on a distal shaft section with an interior in fluid communication with the inflation lumen, and the stent having an open-walled body of stent struts with gaps between adjacent stent struts;
placing the stent and balloon catheter assembly into one half of complementary halves of a split mold having a polished interior bore, and closing the halves to enclose the assembly therein;
applying a first radially compressive force via the split mold on an outer surface of the stent and thereby decreasing the outer diameter of the stent on the balloon catheter;
heating the balloon and introducing inflation media into the interior of the balloon to radially expand the balloon with the stent restrained from radially expanding, wherein the balloon expands into the stent gaps to embed the stent in an outer surface of the balloon;
removing the inflation media from the balloon interior; and
applying a second radially compressive force via the split mold on an outer surface of the stent, thereby decreasing the outer diameter of the stent on the balloon catheter.
10. The method of claim 9, further including sterilizing the stent mounted on the balloon catheter.
11. The method of claim 9, wherein at least one of the radially compressive forces is applied by a crimping apparatus.
12. The method of claim 9, wherein at least one of the radially compressive forces is applied by a hand tool.
13. The method of claim 9, wherein at least one of the radially compressive forces is applied by hand.
14. The method of claim 9, wherein the stent is restrained from radially expanding by a mold.
15. The method of claim 14, wherein the mold is a split mold and the balloon catheter with the stent mounted thereon is removed from the split mold by opening of the split mold.
16. The method of claim 9, further including sterilization of the balloon catheter and stent with ethylene oxide.
17. A method of increasing retention of an intravascular device having a drug coating and having an open-walled body defined by struts and gaps on a balloon catheter, comprising:
a first stage of crimping the intravascular device onto a balloon of the balloon catheter to form an assembly, and placing the intravascular device and balloon catheter assembly into one half of complementary halves of a split mold, and closing the halves to enclose the assembly therein;
a second stage of heating and pressurizing the balloon while restricting radial expansion of an outer surface of the intravascular device via the split mold, wherein the balloon expands into the stent gaps to embed the stent in an outer surface of the balloon; and
a third stage of re-crimping the intravascular device onto the balloon of the balloon catheter via the split mold.
18. The method of claim 17, further including heating the intravascular device and the balloon catheter during the third stage.
19. The method of claim 17, further including pressurizing the balloon catheter during the third stage.
US11453747 2005-04-12 2006-06-15 Method for retaining a vascular stent on a catheter Active 2027-08-20 US7763198B2 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
US11105085 US7563400B2 (en) 2005-04-12 2005-04-12 Method of stent mounting to form a balloon catheter having improved retention of a drug delivery stent
US11453747 US7763198B2 (en) 2005-04-12 2006-06-15 Method for retaining a vascular stent on a catheter

Applications Claiming Priority (10)

Application Number Priority Date Filing Date Title
US11453747 US7763198B2 (en) 2005-04-12 2006-06-15 Method for retaining a vascular stent on a catheter
US11521993 US7947207B2 (en) 2005-04-12 2006-09-15 Method for retaining a vascular stent on a catheter
JP2009515551A JP5184524B2 (en) 2006-06-15 2007-05-17 The method for holding the stent for vascular onto the catheter
EP20070797556 EP2029052B1 (en) 2006-06-15 2007-05-17 Method for retaining a vascular stent on a catheter
PCT/US2007/069175 WO2007146543A3 (en) 2006-06-15 2007-05-17 Method for retaining a vascular stent on a catheter
EP20170164796 EP3207903A1 (en) 2006-06-15 2007-05-17 Method for retaining a vascular stent on a catheter
EP20140163606 EP2752171B1 (en) 2006-06-15 2007-05-17 Method for retaining a vascular stent on a catheter
US12837809 US20100278956A1 (en) 2005-04-12 2010-07-16 Method for retaining a vascular stent on a catheter
US13091847 US8221112B2 (en) 2005-04-12 2011-04-21 Method for retaining a vascular stent on a catheter
US13493260 US8540927B2 (en) 2005-04-12 2012-06-11 Method for retaining a vascular stent on a catheter

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US11105085 Continuation-In-Part US7563400B2 (en) 2005-04-12 2005-04-12 Method of stent mounting to form a balloon catheter having improved retention of a drug delivery stent

Related Child Applications (2)

Application Number Title Priority Date Filing Date
US11521993 Continuation-In-Part US7947207B2 (en) 2005-04-12 2006-09-15 Method for retaining a vascular stent on a catheter
US12837809 Continuation US20100278956A1 (en) 2005-04-12 2010-07-16 Method for retaining a vascular stent on a catheter

Publications (2)

Publication Number Publication Date
US20070204455A1 true US20070204455A1 (en) 2007-09-06
US7763198B2 true US7763198B2 (en) 2010-07-27

Family

ID=38634056

Family Applications (2)

Application Number Title Priority Date Filing Date
US11453747 Active 2027-08-20 US7763198B2 (en) 2005-04-12 2006-06-15 Method for retaining a vascular stent on a catheter
US12837809 Abandoned US20100278956A1 (en) 2005-04-12 2010-07-16 Method for retaining a vascular stent on a catheter

Family Applications After (1)

Application Number Title Priority Date Filing Date
US12837809 Abandoned US20100278956A1 (en) 2005-04-12 2010-07-16 Method for retaining a vascular stent on a catheter

Country Status (4)

Country Link
US (2) US7763198B2 (en)
EP (3) EP2752171B1 (en)
JP (1) JP5184524B2 (en)
WO (1) WO2007146543A3 (en)

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20120079706A1 (en) * 2010-09-30 2012-04-05 Advanced Cardiovascular Systems, Inc. Stent Crimping Methods
US8540927B2 (en) * 2005-04-12 2013-09-24 Abbott Cardiovascular Systems Inc. Method for retaining a vascular stent on a catheter
US8574283B1 (en) * 2011-08-30 2013-11-05 Suraj Govind Kamat Deployment of stents within bifurcated vessels
US9259341B2 (en) 2006-06-19 2016-02-16 Abbott Cardiovascular Systems Inc. Methods for improving stent retention on a balloon catheter
US9295570B2 (en) 2001-09-19 2016-03-29 Abbott Laboratories Vascular Enterprises Limited Cold-molding process for loading a stent onto a stent delivery system
US20160096308A1 (en) * 2014-10-02 2016-04-07 Inspiremd, Ltd Stent thermoforming apparatus and methods

Families Citing this family (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
USRE37377E1 (en) 1992-10-09 2001-09-18 Asahi Glass Company, Ltd. LCD device including an illumination device having a polarized light separating sheet between a light guide and the display
US8393328B2 (en) 2003-08-22 2013-03-12 BiO2 Medical, Inc. Airway assembly and methods of using an airway assembly
US7763198B2 (en) 2005-04-12 2010-07-27 Abbott Cardiovascular Systems Inc. Method for retaining a vascular stent on a catheter
US8099851B2 (en) * 2005-06-27 2012-01-24 Boston Scientific Scimed, Inc. Crimping and edge protection elements
US7886419B2 (en) * 2006-07-18 2011-02-15 Advanced Cardiovascular Systems, Inc. Stent crimping apparatus and method
US8613753B2 (en) 2007-08-31 2013-12-24 BiO2 Medical, Inc. Multi-lumen central access vena cava filter apparatus and method of using same
US8668712B2 (en) 2007-08-31 2014-03-11 BiO2 Medical, Inc. Multi-lumen central access vena cava filter apparatus and method of using same
US9039728B2 (en) 2007-08-31 2015-05-26 BiO2 Medical, Inc. IVC filter catheter with imaging modality
US9687333B2 (en) 2007-08-31 2017-06-27 BiO2 Medical, Inc. Reduced profile central venous access catheter with vena cava filter and method
US20090163985A1 (en) * 2007-12-19 2009-06-25 Vipul Dave Method of Retaining a Polymeric Stent on an Expansion Member
US8597716B2 (en) 2009-06-23 2013-12-03 Abbott Cardiovascular Systems Inc. Methods to increase fracture resistance of a drug-eluting medical device
US8539663B2 (en) 2010-08-23 2013-09-24 Abbott Cardiovascular Systems Inc. Reducing crimping damage to polymer scaffold
JP6050926B2 (en) * 2010-09-22 2016-12-21 株式会社カネカ Method of manufacturing a stent delivery system
US8961848B2 (en) 2011-04-18 2015-02-24 Abbott Cardiovascular Systems Inc. Methods for increasing a retention force between a polymeric scaffold and a delivery balloon
US20120290063A1 (en) 2011-05-09 2012-11-15 Abbott Cardiovascular Systems Inc. Method of Increasing Stent Retention of Bioabsorbable Scaffolding with a Sheath
US20150105723A1 (en) * 2012-03-09 2015-04-16 Clearstream Technologies Limited Parison for forming blow molded medical balloon with modified portion, medical balloon, and related methods
US9199408B2 (en) 2012-04-03 2015-12-01 Abbott Cardiovascular Systems Inc. Uniform crimping and deployment methods for polymer scaffold
JP6026775B2 (en) * 2012-05-25 2016-11-16 株式会社グッドマン Stent delivery catheter
EP3148448B1 (en) 2014-05-28 2018-04-04 Boston Scientific Scimed, Inc. Catheter with radiofrequency cutting tip and heated balloon

Citations (251)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2301559A (en) 1938-10-21 1942-11-10 Hancock Mfg Company Door latch
US3105492A (en) 1958-10-01 1963-10-01 Us Catheter & Instr Corp Synthetic blood vessel grafts
US3657744A (en) 1970-05-08 1972-04-25 Univ Minnesota Method for fixing prosthetic implants in a living body
US3868956A (en) 1972-06-05 1975-03-04 Ralph J Alfidi Vessel implantable appliance and method of implanting it
US3993078A (en) 1974-11-04 1976-11-23 Gambro Ag Insert for use preferably in vascular surgery
US4130904A (en) 1977-06-06 1978-12-26 Thermo Electron Corporation Prosthetic blood conduit
US4140126A (en) 1977-02-18 1979-02-20 Choudhury M Hasan Method for performing aneurysm repair
US4159719A (en) 1977-05-09 1979-07-03 Xomed, Inc. Moisture-expandable ear wick
US4241146A (en) 1978-11-20 1980-12-23 Eugene W. Sivachenko Corrugated plate having variable material thickness and method for making same
GB2070490A (en) 1980-02-26 1981-09-09 Ferranti Ltd Laser cutting apparatus
US4323071A (en) 1978-04-24 1982-04-06 Advanced Catheter Systems, Inc. Vascular guiding catheter assembly and vascular dilating catheter assembly and a combination thereof and methods of making the same
EP0062300A2 (en) 1981-04-06 1982-10-13 FRITZ WITTIG Herstellung gedruckter Schaltungen Process for making a circuit board
US4387952A (en) 1981-03-27 1983-06-14 Spectra-Physics, Inc. Single axis beam scanner
GB2135585A (en) 1982-04-30 1984-09-05 Hans Ivar Wallsten A prosthesis comprising an expansible or contractile tubular body
US4504354A (en) 1982-08-23 1985-03-12 Gravure Research Institute, Inc. Method and apparatus for forming gravure cells in a gravure cylinder
US4503569A (en) 1983-03-03 1985-03-12 Dotter Charles T Transluminally placed expandable graft prosthesis
US4512338A (en) 1983-01-25 1985-04-23 Balko Alexander B Process for restoring patency to body vessels
US4516972A (en) 1982-01-28 1985-05-14 Advanced Cardiovascular Systems, Inc. Guiding catheter and method of manufacture
US4531933A (en) 1982-12-07 1985-07-30 C. R. Bard, Inc. Helical ureteral stent
US4553545A (en) 1981-09-16 1985-11-19 Medinvent S.A. Device for application in blood vessels or other difficultly accessible locations and its use
US4560374A (en) 1983-10-17 1985-12-24 Hammerslag Julius G Method for repairing stenotic vessels
US4580568A (en) 1984-10-01 1986-04-08 Cook, Incorporated Percutaneous endovascular stent and method for insertion thereof
US4616652A (en) 1983-10-19 1986-10-14 Advanced Cardiovascular Systems, Inc. Dilatation catheter positioning apparatus
US4619246A (en) 1984-05-23 1986-10-28 William Cook, Europe A/S Collapsible filter basket
EP0201466A2 (en) 1985-04-10 1986-11-12 Medinvent S.A. Coil spring for transluminal implantation and planar blank for the manufacture thereof
US4650466A (en) 1985-11-01 1987-03-17 Angiobrade Partners Angioplasty device
US4649922A (en) 1986-01-23 1987-03-17 Wiktor Donimik M Catheter arrangement having a variable diameter tip and spring prosthesis
EP0221570A2 (en) 1985-11-07 1987-05-13 Julio C. Palmaz Expandable intraluminal graft, and apparatus for implanting an expandable intraluminal graft
US4665918A (en) 1986-01-06 1987-05-19 Garza Gilbert A Prosthesis system and method
US4665906A (en) 1983-10-14 1987-05-19 Raychem Corporation Medical devices incorporating sim alloy elements
DE3640745A1 (en) 1985-11-30 1987-06-04 Ernst Peter Prof Dr M Strecker Catheter for producing or extending connections to or between body cavities
US4681110A (en) 1985-12-02 1987-07-21 Wiktor Dominik M Catheter arrangement having a blood vessel liner, and method of using it
US4706671A (en) 1985-05-02 1987-11-17 Weinrib Harry P Catheter with coiled tip
US4725334A (en) 1985-05-15 1988-02-16 Chem-Tronics, Inc. Method of forming integrally stiffened structures
US4740207A (en) 1986-09-10 1988-04-26 Kreamer Jeffry W Intralumenal graft
US4748982A (en) 1987-01-06 1988-06-07 Advanced Cardiovascular Systems, Inc. Reinforced balloon dilatation catheter with slitted exchange sleeve and method
US4762128A (en) 1986-12-09 1988-08-09 Advanced Surgical Intervention, Inc. Method and apparatus for treating hypertrophy of the prostate gland
US4767418A (en) 1986-02-13 1988-08-30 California Institute Of Technology Luminal surface fabrication for cardiovascular prostheses
US4768507A (en) 1986-02-24 1988-09-06 Medinnovations, Inc. Intravascular stent and percutaneous insertion catheter system for the dilation of an arterial stenosis and the prevention of arterial restenosis
US4795458A (en) 1987-07-02 1989-01-03 Regan Barrie F Stent for use following balloon angioplasty
DE3823060A1 (en) 1987-07-10 1989-01-19 Nippon Zeon Co catheter
US4800882A (en) 1987-03-13 1989-01-31 Cook Incorporated Endovascular stent and delivery system
WO1989001798A1 (en) 1987-09-02 1989-03-09 Engineers & Doctors A/S Device for the placing of a partial catheter in a body cavity
US4830003A (en) 1988-06-17 1989-05-16 Wolff Rodney G Compressive stent and delivery system
US4848343A (en) 1986-10-31 1989-07-18 Medinvent S.A. Device for transluminal implantation
US4856516A (en) 1989-01-09 1989-08-15 Cordis Corporation Endovascular stent apparatus and method
WO1989008433A1 (en) 1988-03-09 1989-09-21 Lazarus Harrison M Artificial graft and implantation method
US4870966A (en) 1988-02-01 1989-10-03 American Cyanamid Company Bioabsorbable surgical device for treating nerve defects
EP0338816A2 (en) 1988-04-22 1989-10-25 Kawasaki Steel Corporation Process and equipment for micropattern forming on roll surface, metal sheets for pressworking prepared by the roll and methods of preparing same
US4877030A (en) 1988-02-02 1989-10-31 Andreas Beck Device for the widening of blood vessels
US4878906A (en) 1986-03-25 1989-11-07 Servetus Partnership Endoprosthesis for repairing a damaged vessel
US4886062A (en) 1987-10-19 1989-12-12 Medtronic, Inc. Intravascular radially expandable stent and method of implant
US4887997A (en) 1986-11-21 1989-12-19 Sherwood Medical Company Catheter for nasogastric intubation
US4892539A (en) 1988-02-08 1990-01-09 D-R Medical Systems, Inc. Vascular graft
US4893623A (en) 1986-12-09 1990-01-16 Advanced Surgical Intervention, Inc. Method and apparatus for treating hypertrophy of the prostate gland
US4907336A (en) 1987-03-13 1990-03-13 Cook Incorporated Method of making an endovascular stent and delivery system
US4913141A (en) 1988-10-25 1990-04-03 Cordis Corporation Apparatus and method for placement of a stent within a subject vessel
EP0364787A1 (en) 1988-10-04 1990-04-25 EXPANDABLE GRAFTS PARTNERSHIP a Texas General Partnership Expandable intraluminal graft
US4921479A (en) 1987-10-02 1990-05-01 Joseph Grayzel Catheter sheath with longitudinal seam
US4923464A (en) 1985-09-03 1990-05-08 Becton, Dickinson And Company Percutaneously deliverable intravascular reconstruction prosthesis
EP0361192A3 (en) 1988-09-29 1990-06-06 Siemens Aktiengesellschaft Method of making circuit boards
US4950227A (en) 1988-11-07 1990-08-21 Boston Scientific Corporation Stent delivery system
EP0372789A3 (en) 1988-12-02 1990-08-22 General Electric Company Apparatus for machining intricate feature cuts in thin walled tubular parts
US4963022A (en) 1988-10-24 1990-10-16 Zygo Corporation Method and apparatus for generating a straight reference line
US4969458A (en) 1987-07-06 1990-11-13 Medtronic, Inc. Intracoronary stent and method of simultaneous angioplasty and stent implant
EP0408245A1 (en) 1989-07-13 1991-01-16 American Medical Systems, Inc. Stent placement instrument
US4986831A (en) 1988-04-25 1991-01-22 Angeion Corporation Medical implant
US4988356A (en) 1987-02-27 1991-01-29 C. R. Bard, Inc. Catheter and guidewire exchange system
US4990155A (en) 1989-05-19 1991-02-05 Wilkoff Howard M Surgical stent method and apparatus
US4994071A (en) 1989-05-22 1991-02-19 Cordis Corporation Bifurcating stent apparatus and method
US4998539A (en) 1987-12-18 1991-03-12 Delsanti Gerard L Method of using removable endo-arterial devices to repair detachments in the arterial walls
US5002560A (en) 1989-09-08 1991-03-26 Advanced Cardiovascular Systems, Inc. Expandable cage catheter with a rotatable guide
EP0421729A2 (en) 1989-10-02 1991-04-10 Medtronic, Inc. Articulated stent
US5007926A (en) 1989-02-24 1991-04-16 The Trustees Of The University Of Pennsylvania Expandable transluminally implantable tubular prosthesis
EP0423916A1 (en) 1989-10-17 1991-04-24 Cook Incorporated Percutaneous stent
US5015253A (en) 1989-06-15 1991-05-14 Cordis Corporation Non-woven endoprosthesis
EP0428479A1 (en) 1989-11-01 1991-05-22 Schneider (Europe) Ag Stent and catheter for inserting the stent
US5019085A (en) 1988-10-25 1991-05-28 Cordis Corporation Apparatus and method for placement of a stent within a subject vessel
US5019090A (en) 1988-09-01 1991-05-28 Corvita Corporation Radially expandable endoprosthesis and the like
WO1991007139A1 (en) 1989-11-09 1991-05-30 Ian Leonard Producing prostheses
US5034001A (en) 1989-09-08 1991-07-23 Advanced Cardiovascular Systems, Inc. Method of repairing a damaged blood vessel with an expandable cage catheter
US5037392A (en) 1989-06-06 1991-08-06 Cordis Corporation Stent-implanting balloon assembly
US5037427A (en) 1987-03-25 1991-08-06 Terumo Kabushiki Kaisha Method of implanting a stent within a tubular organ of a living body and of removing same
US5037377A (en) 1984-11-28 1991-08-06 Medtronic, Inc. Means for improving biocompatibility of implants, particularly of vascular grafts
US5041126A (en) 1987-03-13 1991-08-20 Cook Incorporated Endovascular stent and delivery system
US5059211A (en) 1987-06-25 1991-10-22 Duke University Absorbable vascular stent
US5061275A (en) 1986-04-21 1991-10-29 Medinvent S.A. Self-expanding prosthesis
US5061273A (en) 1989-06-01 1991-10-29 Yock Paul G Angioplasty apparatus facilitating rapid exchanges
US5062829A (en) 1989-03-17 1991-11-05 Carter Holt Harvey Plastic Products Group Limited Relates to devices for administering a substance such as a drug or chemical or the like
US5064435A (en) 1990-06-28 1991-11-12 Schneider (Usa) Inc. Self-expanding prosthesis having stable axial length
US5067957A (en) 1983-10-14 1991-11-26 Raychem Corporation Method of inserting medical devices incorporating SIM alloy elements
US5071407A (en) 1990-04-12 1991-12-10 Schneider (U.S.A.) Inc. Radially expandable fixation member
US5073694A (en) 1991-02-21 1991-12-17 Synthes (U.S.A.) Method and apparatus for laser cutting a hollow metal workpiece
US5078726A (en) 1989-02-01 1992-01-07 Kreamer Jeffry W Graft stent and method of repairing blood vessels
US5078736A (en) 1990-05-04 1992-01-07 Interventional Thermodynamics, Inc. Method and apparatus for maintaining patency in the body passages
US5084065A (en) 1989-07-10 1992-01-28 Corvita Corporation Reinforced graft assembly
US5089005A (en) 1987-08-13 1992-02-18 Terumo Kabushiki Kaisha Catheter for the introduction of an expandable member
US5089006A (en) 1989-11-29 1992-02-18 Stiles Frank B Biological duct liner and installation catheter
US5092877A (en) 1988-09-01 1992-03-03 Corvita Corporation Radially expandable endoprosthesis
EP0407951A3 (en) 1989-07-10 1992-03-04 Shipley Company Inc. Method for applying a photoresist to a 3-d conductive substrate
US5100429A (en) 1989-04-28 1992-03-31 C. R. Bard, Inc. Endovascular stent and delivery system
US5102417A (en) 1985-11-07 1992-04-07 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
US5108417A (en) 1990-09-14 1992-04-28 Interface Biomedical Laboratories Corp. Anti-turbulent, anti-thrombogenic intravascular stent
US5108416A (en) 1990-02-13 1992-04-28 C. R. Bard, Inc. Stent introducer system
WO1992006734A1 (en) 1990-10-18 1992-04-30 Ho Young Song Self-expanding endovascular stent
US5116318A (en) 1989-06-06 1992-05-26 Cordis Corporation Dilatation balloon within an elastic sleeve
US5116360A (en) 1990-12-27 1992-05-26 Corvita Corporation Mesh composite graft
US5116365A (en) 1991-02-22 1992-05-26 Cordis Corporation Stent apparatus and method for making
WO1992009246A1 (en) 1990-11-28 1992-06-11 Numed, Inc. Intravascular radially expandable stent and method
US5122154A (en) 1990-08-15 1992-06-16 Rhodes Valentine J Endovascular bypass graft
US5123917A (en) 1990-04-27 1992-06-23 Lee Peter Y Expandable intraluminal vascular graft
US5133732A (en) 1987-10-19 1992-07-28 Medtronic, Inc. Intravascular stent
US5135536A (en) 1991-02-05 1992-08-04 Cordis Corporation Endovascular stent and method
US5158548A (en) 1990-04-25 1992-10-27 Advanced Cardiovascular Systems, Inc. Method and system for stent delivery
US5163951A (en) 1990-12-27 1992-11-17 Corvita Corporation Mesh composite graft
US5163952A (en) 1990-09-14 1992-11-17 Michael Froix Expandable polymeric stent with memory and delivery apparatus and method
US5163958A (en) 1989-02-02 1992-11-17 Cordis Corporation Carbon coated tubular endoprosthesis
EP0517075A1 (en) 1991-06-06 1992-12-09 Advanced Cardiovascular Systems, Inc. Intravascular catheter with a nontraumatic distal tip
US5171262A (en) 1989-06-15 1992-12-15 Cordis Corporation Non-woven endoprosthesis
FR2677872A1 (en) 1991-06-19 1992-12-24 Celsa Lg Device for assisting in the positioning of a filter for trapping thrombi
US5180368A (en) 1989-09-08 1993-01-19 Advanced Cardiovascular Systems, Inc. Rapidly exchangeable and expandable cage catheter for repairing damaged blood vessels
US5183085A (en) 1991-09-27 1993-02-02 Hans Timmermans Method and apparatus for compressing a stent prior to insertion
US5192307A (en) 1987-12-08 1993-03-09 Wall W Henry Angioplasty stent
US5192297A (en) 1991-12-31 1993-03-09 Medtronic, Inc. Apparatus and method for placement and implantation of a stent
US5192311A (en) 1988-04-25 1993-03-09 Angeion Corporation Medical implant and method of making
US5197978A (en) 1991-04-26 1993-03-30 Advanced Coronary Technology, Inc. Removable heat-recoverable tissue supporting device
EP0540290A2 (en) 1991-10-28 1993-05-05 Advanced Cardiovascular Systems, Inc. Expandable stents and method for making same
EP0541443A1 (en) 1991-11-08 1993-05-12 Meadox Medicals, Inc. Endoprosthesis for transluminal implantation
US5217482A (en) 1990-08-28 1993-06-08 Scimed Life Systems, Inc. Balloon catheter with distal guide wire lumen
US5222971A (en) 1990-10-09 1993-06-29 Scimed Life Systems, Inc. Temporary stent and methods for use and manufacture
US5226913A (en) 1988-09-01 1993-07-13 Corvita Corporation Method of making a radially expandable prosthesis
US5234456A (en) 1990-02-08 1993-08-10 Pfizer Hospital Products Group, Inc. Hydrophilic stent
US5242399A (en) 1990-04-25 1993-09-07 Advanced Cardiovascular Systems, Inc. Method and system for stent delivery
US5242397A (en) 1989-06-20 1993-09-07 Cedars-Sinai Medical Center Catheter device and method of use for intramural delivery of protein kinase C and tyrosine protein kinase inhibitors to prevent restenosis after balloon angioplasty
US5242452A (en) 1991-10-11 1993-09-07 Kanji Inoue Device for collapsing an appliance collapsible for insertion into human organs
US5282823A (en) 1992-03-19 1994-02-01 Medtronic, Inc. Intravascular radially expandable stent
US5282824A (en) 1990-10-09 1994-02-01 Cook, Incorporated Percutaneous stent assembly
US5290305A (en) 1991-10-11 1994-03-01 Kanji Inoue Appliance collapsible for insertion into human organs and capable of resilient restoration
US5290295A (en) 1992-07-15 1994-03-01 Querals & Fine, Inc. Insertion tool for an intraluminal graft procedure
US5292331A (en) 1989-08-24 1994-03-08 Applied Vascular Engineering, Inc. Endovascular support device
US5304200A (en) 1991-05-29 1994-04-19 Cordis Corporation Welded radially expandable endoprosthesis and the like
US5314472A (en) 1991-10-01 1994-05-24 Cook Incorporated Vascular stent
EP0606165A1 (en) 1993-01-06 1994-07-13 Ethicon Inc. Stent
WO1994017754A1 (en) 1993-02-04 1994-08-18 Angiomed Ag Stent
US5344425A (en) 1990-09-14 1994-09-06 Interface Biomedical Laboratories, Corp. Intravascular stent and method for conditioning the surfaces thereof
US5344426A (en) 1990-04-25 1994-09-06 Advanced Cardiovascular Systems, Inc. Method and system for stent delivery
US5354308A (en) 1992-05-01 1994-10-11 Beth Israel Hospital Association Metal wire stent
US5356433A (en) 1991-08-13 1994-10-18 Cordis Corporation Biocompatible metal surfaces
US5360401A (en) 1993-02-18 1994-11-01 Advanced Cardiovascular Systems, Inc. Catheter for stent delivery
US5368566A (en) 1992-04-29 1994-11-29 Cardiovascular Dynamics, Inc. Delivery and temporary stent catheter having a reinforced perfusion lumen
US5372600A (en) 1991-10-31 1994-12-13 Instent Inc. Stent delivery systems
US5378239A (en) 1990-04-12 1995-01-03 Schneider (Usa) Inc. Radially expandable fixation member constructed of recovery metal
US5395390A (en) 1992-05-01 1995-03-07 The Beth Israel Hospital Association Metal wire stent
US5405378A (en) 1992-05-20 1995-04-11 Strecker; Ernst P. Device with a prosthesis implantable in the body of a patient
US5413597A (en) 1990-12-29 1995-05-09 Krajicek; Milan Three-layer vascular prostheses
US5423745A (en) 1988-04-28 1995-06-13 Research Medical, Inc. Irregular surface balloon catheters for body passageways and methods of use
US5423885A (en) 1992-01-31 1995-06-13 Advanced Cardiovascular Systems, Inc. Stent capable of attachment within a body lumen
US5445646A (en) 1993-10-22 1995-08-29 Scimed Lifesystems, Inc. Single layer hydraulic sheath stent delivery apparatus and method
WO1995023563A1 (en) 1994-03-04 1995-09-08 Universite De Montreal Endovascular hepatic prostheses
US5449373A (en) 1994-03-17 1995-09-12 Medinol Ltd. Articulated stent
US5456694A (en) 1994-05-13 1995-10-10 Stentco, Inc. Device for delivering and deploying intraluminal devices
WO1995026695A2 (en) 1994-04-01 1995-10-12 Prograft Medical, Inc. Self-expandable stent and stent-graft and method of using them
US5458615A (en) 1993-07-06 1995-10-17 Advanced Cardiovascular Systems, Inc. Stent delivery system
US5476506A (en) 1994-02-08 1995-12-19 Ethicon, Inc. Bi-directional crimped graft
EP0688545A1 (en) 1994-06-17 1995-12-27 Terumo Kabushiki Kaisha Indwelling stent and the method for manufacturing the same
US5484449A (en) 1992-01-07 1996-01-16 Medtronic, Inc. Temporary support for a body lumen and method
WO1996009013A1 (en) 1994-09-21 1996-03-28 Wake Forest University Expandable, intraluminal stents
US5507768A (en) 1991-01-28 1996-04-16 Advanced Cardiovascular Systems, Inc. Stent delivery system
US5527324A (en) 1994-09-07 1996-06-18 Krantz; Kermit E. Surgical stent
US5545132A (en) 1993-12-21 1996-08-13 C. R. Bard, Inc. Helically grooved balloon for dilatation catheter and method of using
WO1996026689A1 (en) 1995-03-01 1996-09-06 Scimed Life Systems, Inc. Improved longitudinally flexible expandable stent
US5569295A (en) 1993-12-28 1996-10-29 Advanced Cardiovascular Systems, Inc. Expandable stents and method for making same
US5571135A (en) 1993-10-22 1996-11-05 Scimed Life Systems Inc. Stent delivery apparatus and method
EP0380668B1 (en) 1987-10-08 1996-12-27 Terumo Kabushiki Kaisha Instrument and apparatus for securing inner diameter of lumen of tubular organ
DE19537872A1 (en) 1995-10-11 1997-04-17 Eckhard Prof Dr Alt Expandable support for blood vessels
US5626604A (en) 1995-12-05 1997-05-06 Cordis Corporation Hand held stent crimping device
US5653691A (en) 1996-04-25 1997-08-05 Rupp; Garry Eugene Thickened inner lumen for uniform stent expansion and method of making
US5653690A (en) 1992-12-30 1997-08-05 Medtronic, Inc. Catheter having a balloon with retention enhancement
EP0800801A1 (en) 1996-04-10 1997-10-15 Advanced Cardiovascular Systems, Inc. Stent having varied amounts of structural strength along its length
US5693089A (en) 1995-04-12 1997-12-02 Inoue; Kanji Method of collapsing an implantable appliance
US5716396A (en) 1993-09-16 1998-02-10 Cordis Corporation Endoprosthesis having multiple laser welded junctions method and procedure
US5716393A (en) 1994-05-26 1998-02-10 Angiomed Gmbh & Co. Medizintechnik Kg Stent with an end of greater diameter than its main body
US5720726A (en) 1992-12-30 1998-02-24 Medtronic, Inc. Balloon catheter having retention enhancements on the balloon
US5733325A (en) 1993-11-04 1998-03-31 C. R. Bard, Inc. Non-migrating vascular prosthesis and minimally invasive placement system
US5733303A (en) 1994-03-17 1998-03-31 Medinol Ltd. Flexible expandable stent
US5741327A (en) 1997-05-06 1998-04-21 Global Therapeutics, Inc. Surgical stent featuring radiopaque markers
US5746765A (en) 1992-05-01 1998-05-05 Nitinol Medical Technologies, Inc. Stent and method and apparatus for forming and delivering the same
WO1998022159A2 (en) 1996-11-07 1998-05-28 Medtronic Instent Inc. Variable flexibility stent
US5776161A (en) 1995-10-16 1998-07-07 Instent, Inc. Medical stents, apparatus and method for making same
US5800521A (en) 1994-11-09 1998-09-01 Endotex Interventional Systems, Inc. Prosthetic graft and method for aneurysm repair
US5800526A (en) 1995-03-17 1998-09-01 Endotex Interventional Systems, Inc. Multi-anchor stent
US5810871A (en) 1997-04-29 1998-09-22 Medtronic, Inc. Stent delivery system
US5810868A (en) 1995-12-07 1998-09-22 Arterial Vascular Engineering, Inc. Stent for improved transluminal deployment
US5817152A (en) 1994-10-19 1998-10-06 Birdsall; Matthew Connected stent apparatus
US5827321A (en) 1997-02-07 1998-10-27 Cornerstone Devices, Inc. Non-Foreshortening intraluminal prosthesis
US5830217A (en) 1996-08-09 1998-11-03 Thomas J. Fogarty Soluble fixation device and method for stent delivery catheters
WO1998048734A1 (en) 1997-04-25 1998-11-05 Jang G David Intravascular stent
US5836965A (en) 1994-10-19 1998-11-17 Jendersee; Brad Stent delivery and deployment method
US5836966A (en) 1997-05-22 1998-11-17 Scimed Life Systems, Inc. Variable expansion force stent
US5855600A (en) 1997-08-01 1999-01-05 Inflow Dynamics Inc. Flexible implantable stent with composite design
US5861027A (en) 1996-04-10 1999-01-19 Variomed Ag Stent for the transluminal implantation in hollow organs
WO1999002105A1 (en) 1997-07-08 1999-01-21 Novo Rps Ulc Expandable stent
EP0916318A1 (en) 1997-10-16 1999-05-19 SciMed Life Systems, Inc. Stent crimper
US5906640A (en) 1994-11-03 1999-05-25 Divysio Solutions Ulc Bifurcated stent and method for the manufacture and delivery of same
US5911452A (en) * 1997-02-04 1999-06-15 Advanced Cardiovascular Systems, Inc. Apparatus and method for mounting a stent onto a catheter
US5911754A (en) 1998-07-24 1999-06-15 Uni-Cath Inc. Flexible stent with effective strut and connector patterns
US5922021A (en) 1996-04-26 1999-07-13 Jang; G. David Intravascular stent
US5925061A (en) 1997-01-13 1999-07-20 Gore Enterprise Holdings, Inc. Low profile vascular stent
US5931851A (en) 1998-04-21 1999-08-03 Advanced Cardiovascular Systems, Inc. Method and apparatus for rubber-tube crimping tool with premount stent
US5938697A (en) 1998-03-04 1999-08-17 Scimed Life Systems, Inc. Stent having variable properties
US5948016A (en) 1997-09-25 1999-09-07 Jang; G. David Intravascular stent with non-parallel slots
US5954743A (en) 1996-04-26 1999-09-21 Jang; G. David Intravascular stent
US5984964A (en) 1993-04-13 1999-11-16 Boston Scientific Corporation Prothesis delivery system
US5997468A (en) 1990-02-28 1999-12-07 Medtronic, Inc. Intraluminal drug eluting prosthesis method
US6010530A (en) 1995-06-07 2000-01-04 Boston Scientific Technology, Inc. Self-expanding endoluminal prosthesis
US6017365A (en) 1997-05-20 2000-01-25 Jomed Implantate Gmbh Coronary stent
US6033435A (en) 1997-11-03 2000-03-07 Divysio Solutions Ulc Bifurcated stent and method for the manufacture and delivery of same
US6042597A (en) 1998-10-23 2000-03-28 Scimed Life Systems, Inc. Helical stent design
US6042606A (en) 1997-09-29 2000-03-28 Cook Incorporated Radially expandable non-axially contracting surgical stent
US6048361A (en) 1997-05-17 2000-04-11 Jomed Implantate Gmbh Balloon catheter and multi-guidewire stent for implanting in the region of branched vessels
US6059822A (en) 1997-08-22 2000-05-09 Uni-Cath Inc. Stent with different mesh patterns
US6063092A (en) * 1998-04-07 2000-05-16 Medtronic Inc. Heat set and crimping process to optimize stent retention
US6071298A (en) 1996-03-22 2000-06-06 Arterial Vascular Engineering Inc. Stents for supporting lumens in living tissue
US6071308A (en) 1997-10-01 2000-06-06 Boston Scientific Corporation Flexible metal wire stent
US6146358A (en) 1989-03-14 2000-11-14 Cordis Corporation Method and apparatus for delivery of therapeutic agent
US6179867B1 (en) 1998-01-16 2001-01-30 Advanced Cardiovascular Systems, Inc. Flexible stent and method of use
US6183506B1 (en) 1996-03-05 2001-02-06 Divysio Solutions Ltd. Expandable stent and method for delivery of same
US6200337B1 (en) 1996-03-10 2001-03-13 Terumo Kabushiki Kaisha Implanting stent
US6206910B1 (en) 1997-09-11 2001-03-27 Wake Forest University Compliant intraluminal stents
US6231598B1 (en) 1997-09-24 2001-05-15 Med Institute, Inc. Radially expandable stent
US6273911B1 (en) 1999-04-22 2001-08-14 Advanced Cardiovascular Systems, Inc. Variable strength stent
US6273901B1 (en) 1999-08-10 2001-08-14 Scimed Life Systems, Inc. Thrombosis filter having a surface treatment
US6273910B1 (en) 1999-03-11 2001-08-14 Advanced Cardiovascular Systems, Inc. Stent with varying strut geometry
US6287336B1 (en) 1995-10-16 2001-09-11 Medtronic, Inc. Variable flexibility stent
US6293959B1 (en) * 1998-11-16 2001-09-25 Cordis Corporation Balloon catheter and stent delivery system having enhanced stent retention and method
US6340366B2 (en) 1998-12-08 2002-01-22 Bandula Wijay Stent with nested or overlapping rings
US6344055B1 (en) 1997-05-14 2002-02-05 Novo Rps Ulc Method for production of an expandable stent
US20030204238A1 (en) 2002-04-26 2003-10-30 Eugene Tedeschi Coated stent with crimpable coating
US20030208254A1 (en) 2002-05-03 2003-11-06 James Shortt Method and apparatus for mounting a stent onto a stent delivery system
US20040177805A1 (en) 2001-03-29 2004-09-16 Luuk Hijlkema Thermal regulation of a coated work-piece during the reconfiguration of the coated work-piece
US6823576B2 (en) 1999-09-22 2004-11-30 Scimed Life Systems, Inc. Method and apparatus for contracting, loading or crimping self-expanding and balloon expandable stent devices
US6863683B2 (en) 2001-09-19 2005-03-08 Abbott Laboratoris Vascular Entities Limited Cold-molding process for loading a stent onto a stent delivery system
US6881216B2 (en) 1996-08-23 2005-04-19 Boston Scientific Scimed, Inc. Balloon catheter with stent securement means
WO2005053937A1 (en) 2003-12-01 2005-06-16 Advanced Cardiovascular Systems, Inc. Temperature controlled crimping
US6955658B2 (en) 2003-01-23 2005-10-18 Medtronic Vascular, Inc. Mold for forming a medical balloon
US7004966B2 (en) 1998-09-30 2006-02-28 C. R. Bard, Inc. Selective adherence of stent-graft coverings
US7021114B2 (en) 2004-04-16 2006-04-04 Boston Scientific Scimed, Inc. Stent crimper
US20060100694A1 (en) 2002-06-13 2006-05-11 Oren Globerman Guidewire system
US7056323B2 (en) 1999-03-31 2006-06-06 Scimed Life Systems, Inc. Stent security balloon/balloon catheter
US7060218B2 (en) 2001-03-06 2006-06-13 Advanced Cardiovascular Systems, Inc. Adjustable length mold assemblies
WO2006110861A8 (en) 2005-04-12 2007-05-03 Advanced Cardiovascular System Method of stent mounting to form a balloon catheter having improved retention of a drug delivery stent

Family Cites Families (17)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2701559A (en) * 1951-08-02 1955-02-08 William A Cooper Apparatus for exfoliating and collecting diagnostic material from inner walls of hollow viscera
US3421184A (en) * 1966-09-21 1969-01-14 Youngstown Sheet And Tube Co Clamps for molds
US4870030A (en) * 1987-09-24 1989-09-26 Research Triangle Institute, Inc. Remote plasma enhanced CVD method for growing an epitaxial semiconductor layer
DE3732874A1 (en) * 1987-09-30 1989-04-20 Thomson Brandt Gmbh An optical pickup
US5078720A (en) * 1990-05-02 1992-01-07 American Medical Systems, Inc. Stent placement instrument and method
US6010539A (en) * 1996-04-01 2000-01-04 E. I. Du Pont De Nemours And Company Cleaning formulations for textile fabrics
US6364870B1 (en) * 1998-12-22 2002-04-02 Medinol Ltd. Apparatus and method for securing a stent on a balloon
US6840081B2 (en) 2000-08-10 2005-01-11 Advanced Cardiovascular Systems, Inc. Assembly for crimping an intraluminal device or measuring the radial strength of the intraluminal device and method of use
CA2355477A1 (en) 2000-08-23 2002-02-23 Cordis Corporation Low profile mounting method for low profile balloon expandable stents
DK1359966T3 (en) * 2001-02-16 2009-10-05 Cordis Corp A process for the preparation of a ballonkarteterindföringssystem with grooves
US6666880B1 (en) * 2001-06-19 2003-12-23 Advised Cardiovascular Systems, Inc. Method and system for securing a coated stent to a balloon catheter
DE10244847A1 (en) * 2002-09-20 2004-04-01 Ulrich Prof. Dr. Speck A medical device for drug delivery
US6702845B1 (en) * 2003-01-17 2004-03-09 Gore Enterprise Holdings, Inc. Compacted implantable medical devices and method of compacting such devices
US6958073B2 (en) * 2003-04-21 2005-10-25 Medtronic Vascular, Inc. Method and system for stent retention using an adhesive
US7055237B2 (en) * 2003-09-29 2006-06-06 Medtronic Vascular, Inc. Method of forming a drug eluting stent
US20050118344A1 (en) * 2003-12-01 2005-06-02 Pacetti Stephen D. Temperature controlled crimping
US7763198B2 (en) 2005-04-12 2010-07-27 Abbott Cardiovascular Systems Inc. Method for retaining a vascular stent on a catheter

Patent Citations (291)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2301559A (en) 1938-10-21 1942-11-10 Hancock Mfg Company Door latch
US3105492A (en) 1958-10-01 1963-10-01 Us Catheter & Instr Corp Synthetic blood vessel grafts
US3657744A (en) 1970-05-08 1972-04-25 Univ Minnesota Method for fixing prosthetic implants in a living body
US3868956A (en) 1972-06-05 1975-03-04 Ralph J Alfidi Vessel implantable appliance and method of implanting it
US3993078A (en) 1974-11-04 1976-11-23 Gambro Ag Insert for use preferably in vascular surgery
US4140126A (en) 1977-02-18 1979-02-20 Choudhury M Hasan Method for performing aneurysm repair
US4159719A (en) 1977-05-09 1979-07-03 Xomed, Inc. Moisture-expandable ear wick
US4130904A (en) 1977-06-06 1978-12-26 Thermo Electron Corporation Prosthetic blood conduit
US4323071B1 (en) 1978-04-24 1990-05-29 Advanced Cardiovascular System
US4323071A (en) 1978-04-24 1982-04-06 Advanced Catheter Systems, Inc. Vascular guiding catheter assembly and vascular dilating catheter assembly and a combination thereof and methods of making the same
US4241146A (en) 1978-11-20 1980-12-23 Eugene W. Sivachenko Corrugated plate having variable material thickness and method for making same
GB2070490A (en) 1980-02-26 1981-09-09 Ferranti Ltd Laser cutting apparatus
US4387952A (en) 1981-03-27 1983-06-14 Spectra-Physics, Inc. Single axis beam scanner
EP0062300A2 (en) 1981-04-06 1982-10-13 FRITZ WITTIG Herstellung gedruckter Schaltungen Process for making a circuit board
US4553545A (en) 1981-09-16 1985-11-19 Medinvent S.A. Device for application in blood vessels or other difficultly accessible locations and its use
US4516972A (en) 1982-01-28 1985-05-14 Advanced Cardiovascular Systems, Inc. Guiding catheter and method of manufacture
US4655771B1 (en) 1982-04-30 1996-09-10 Medinvent Ams Sa Prosthesis comprising an expansible or contractile tubular body
GB2135585A (en) 1982-04-30 1984-09-05 Hans Ivar Wallsten A prosthesis comprising an expansible or contractile tubular body
US4655771A (en) 1982-04-30 1987-04-07 Shepherd Patents S.A. Prosthesis comprising an expansible or contractile tubular body
US4504354A (en) 1982-08-23 1985-03-12 Gravure Research Institute, Inc. Method and apparatus for forming gravure cells in a gravure cylinder
US4531933A (en) 1982-12-07 1985-07-30 C. R. Bard, Inc. Helical ureteral stent
US4512338A (en) 1983-01-25 1985-04-23 Balko Alexander B Process for restoring patency to body vessels
US4503569A (en) 1983-03-03 1985-03-12 Dotter Charles T Transluminally placed expandable graft prosthesis
US4665906A (en) 1983-10-14 1987-05-19 Raychem Corporation Medical devices incorporating sim alloy elements
US5067957A (en) 1983-10-14 1991-11-26 Raychem Corporation Method of inserting medical devices incorporating SIM alloy elements
US4560374A (en) 1983-10-17 1985-12-24 Hammerslag Julius G Method for repairing stenotic vessels
US4616652A (en) 1983-10-19 1986-10-14 Advanced Cardiovascular Systems, Inc. Dilatation catheter positioning apparatus
US6030413A (en) 1983-12-09 2000-02-29 Endovascular Technologies, Inc. Artificial graft and implantation method
US4619246A (en) 1984-05-23 1986-10-28 William Cook, Europe A/S Collapsible filter basket
US4580568A (en) 1984-10-01 1986-04-08 Cook, Incorporated Percutaneous endovascular stent and method for insertion thereof
US5037377A (en) 1984-11-28 1991-08-06 Medtronic, Inc. Means for improving biocompatibility of implants, particularly of vascular grafts
US4760849A (en) 1985-04-10 1988-08-02 Medinvent S.A. Planar blank and a coil spring manufactured therefrom
EP0201466A2 (en) 1985-04-10 1986-11-12 Medinvent S.A. Coil spring for transluminal implantation and planar blank for the manufacture thereof
US4706671A (en) 1985-05-02 1987-11-17 Weinrib Harry P Catheter with coiled tip
US4725334A (en) 1985-05-15 1988-02-16 Chem-Tronics, Inc. Method of forming integrally stiffened structures
US4923464A (en) 1985-09-03 1990-05-08 Becton, Dickinson And Company Percutaneously deliverable intravascular reconstruction prosthesis
US4650466A (en) 1985-11-01 1987-03-17 Angiobrade Partners Angioplasty device
US4776337B1 (en) 1985-11-07 2000-12-05 Cordis Corp Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft
US4733665B1 (en) 1985-11-07 1994-01-11 Expandable Grafts Partnership Expandable intraluminal graft,and method and apparatus for implanting an expandable intraluminal graft
US4733665A (en) 1985-11-07 1988-03-29 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
EP0221570A2 (en) 1985-11-07 1987-05-13 Julio C. Palmaz Expandable intraluminal graft, and apparatus for implanting an expandable intraluminal graft
US4733665C2 (en) 1985-11-07 2002-01-29 Expandable Grafts Partnership Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft
US4739762B1 (en) 1985-11-07 1998-10-27 Expandable Grafts Partnership Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft
US4776337A (en) 1985-11-07 1988-10-11 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
US5102417A (en) 1985-11-07 1992-04-07 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
US4739762A (en) 1985-11-07 1988-04-26 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
DE3640745A1 (en) 1985-11-30 1987-06-04 Ernst Peter Prof Dr M Strecker Catheter for producing or extending connections to or between body cavities
US4922905A (en) 1985-11-30 1990-05-08 Strecker Ernst P Dilatation catheter
US4681110A (en) 1985-12-02 1987-07-21 Wiktor Dominik M Catheter arrangement having a blood vessel liner, and method of using it
US4665918A (en) 1986-01-06 1987-05-19 Garza Gilbert A Prosthesis system and method
US4649922A (en) 1986-01-23 1987-03-17 Wiktor Donimik M Catheter arrangement having a variable diameter tip and spring prosthesis
US4767418A (en) 1986-02-13 1988-08-30 California Institute Of Technology Luminal surface fabrication for cardiovascular prostheses
US4768507A (en) 1986-02-24 1988-09-06 Medinnovations, Inc. Intravascular stent and percutaneous insertion catheter system for the dilation of an arterial stenosis and the prevention of arterial restenosis
US4878906A (en) 1986-03-25 1989-11-07 Servetus Partnership Endoprosthesis for repairing a damaged vessel
US5061275A (en) 1986-04-21 1991-10-29 Medinvent S.A. Self-expanding prosthesis
US4740207A (en) 1986-09-10 1988-04-26 Kreamer Jeffry W Intralumenal graft
US4848343A (en) 1986-10-31 1989-07-18 Medinvent S.A. Device for transluminal implantation
US4887997A (en) 1986-11-21 1989-12-19 Sherwood Medical Company Catheter for nasogastric intubation
US4762128A (en) 1986-12-09 1988-08-09 Advanced Surgical Intervention, Inc. Method and apparatus for treating hypertrophy of the prostate gland
US4893623A (en) 1986-12-09 1990-01-16 Advanced Surgical Intervention, Inc. Method and apparatus for treating hypertrophy of the prostate gland
US4748982A (en) 1987-01-06 1988-06-07 Advanced Cardiovascular Systems, Inc. Reinforced balloon dilatation catheter with slitted exchange sleeve and method
US4988356A (en) 1987-02-27 1991-01-29 C. R. Bard, Inc. Catheter and guidewire exchange system
US4907336A (en) 1987-03-13 1990-03-13 Cook Incorporated Method of making an endovascular stent and delivery system
US5041126A (en) 1987-03-13 1991-08-20 Cook Incorporated Endovascular stent and delivery system
US4800882A (en) 1987-03-13 1989-01-31 Cook Incorporated Endovascular stent and delivery system
US5314444A (en) 1987-03-13 1994-05-24 Cook Incorporated Endovascular stent and delivery system
US5037427A (en) 1987-03-25 1991-08-06 Terumo Kabushiki Kaisha Method of implanting a stent within a tubular organ of a living body and of removing same
US5059211A (en) 1987-06-25 1991-10-22 Duke University Absorbable vascular stent
US4795458A (en) 1987-07-02 1989-01-03 Regan Barrie F Stent for use following balloon angioplasty
US4969458A (en) 1987-07-06 1990-11-13 Medtronic, Inc. Intracoronary stent and method of simultaneous angioplasty and stent implant
DE3823060A1 (en) 1987-07-10 1989-01-19 Nippon Zeon Co catheter
US4969890A (en) 1987-07-10 1990-11-13 Nippon Zeon Co., Ltd. Catheter
US5089005A (en) 1987-08-13 1992-02-18 Terumo Kabushiki Kaisha Catheter for the introduction of an expandable member
WO1989001798A1 (en) 1987-09-02 1989-03-09 Engineers & Doctors A/S Device for the placing of a partial catheter in a body cavity
US4921479A (en) 1987-10-02 1990-05-01 Joseph Grayzel Catheter sheath with longitudinal seam
EP0380668B1 (en) 1987-10-08 1996-12-27 Terumo Kabushiki Kaisha Instrument and apparatus for securing inner diameter of lumen of tubular organ
US5653727A (en) 1987-10-19 1997-08-05 Medtronic, Inc. Intravascular stent
US4886062A (en) 1987-10-19 1989-12-12 Medtronic, Inc. Intravascular radially expandable stent and method of implant
US5133732A (en) 1987-10-19 1992-07-28 Medtronic, Inc. Intravascular stent
US5192307A (en) 1987-12-08 1993-03-09 Wall W Henry Angioplasty stent
US4998539A (en) 1987-12-18 1991-03-12 Delsanti Gerard L Method of using removable endo-arterial devices to repair detachments in the arterial walls
US4870966A (en) 1988-02-01 1989-10-03 American Cyanamid Company Bioabsorbable surgical device for treating nerve defects
US4877030A (en) 1988-02-02 1989-10-31 Andreas Beck Device for the widening of blood vessels
US4892539A (en) 1988-02-08 1990-01-09 D-R Medical Systems, Inc. Vascular graft
WO1989008433A1 (en) 1988-03-09 1989-09-21 Lazarus Harrison M Artificial graft and implantation method
EP0338816A2 (en) 1988-04-22 1989-10-25 Kawasaki Steel Corporation Process and equipment for micropattern forming on roll surface, metal sheets for pressworking prepared by the roll and methods of preparing same
US5192311A (en) 1988-04-25 1993-03-09 Angeion Corporation Medical implant and method of making
US4986831A (en) 1988-04-25 1991-01-22 Angeion Corporation Medical implant
US5423745A (en) 1988-04-28 1995-06-13 Research Medical, Inc. Irregular surface balloon catheters for body passageways and methods of use
US4830003A (en) 1988-06-17 1989-05-16 Wolff Rodney G Compressive stent and delivery system
US5019090A (en) 1988-09-01 1991-05-28 Corvita Corporation Radially expandable endoprosthesis and the like
US5226913A (en) 1988-09-01 1993-07-13 Corvita Corporation Method of making a radially expandable prosthesis
US5092877A (en) 1988-09-01 1992-03-03 Corvita Corporation Radially expandable endoprosthesis
US4943346A (en) 1988-09-29 1990-07-24 Siemens Aktiengesellschaft Method for manufacturing printed circuit boards
EP0361192A3 (en) 1988-09-29 1990-06-06 Siemens Aktiengesellschaft Method of making circuit boards
US5902332A (en) 1988-10-04 1999-05-11 Expandable Grafts Partnership Expandable intraluminal graft
EP0364787A1 (en) 1988-10-04 1990-04-25 EXPANDABLE GRAFTS PARTNERSHIP a Texas General Partnership Expandable intraluminal graft
US5195984A (en) 1988-10-04 1993-03-23 Expandable Grafts Partnership Expandable intraluminal graft
US4963022A (en) 1988-10-24 1990-10-16 Zygo Corporation Method and apparatus for generating a straight reference line
US4913141A (en) 1988-10-25 1990-04-03 Cordis Corporation Apparatus and method for placement of a stent within a subject vessel
US5019085A (en) 1988-10-25 1991-05-28 Cordis Corporation Apparatus and method for placement of a stent within a subject vessel
US4950227A (en) 1988-11-07 1990-08-21 Boston Scientific Corporation Stent delivery system
EP0372789A3 (en) 1988-12-02 1990-08-22 General Electric Company Apparatus for machining intricate feature cuts in thin walled tubular parts
US4856516A (en) 1989-01-09 1989-08-15 Cordis Corporation Endovascular stent apparatus and method
US5078726A (en) 1989-02-01 1992-01-07 Kreamer Jeffry W Graft stent and method of repairing blood vessels
US5163958A (en) 1989-02-02 1992-11-17 Cordis Corporation Carbon coated tubular endoprosthesis
US5007926A (en) 1989-02-24 1991-04-16 The Trustees Of The University Of Pennsylvania Expandable transluminally implantable tubular prosthesis
US6146358A (en) 1989-03-14 2000-11-14 Cordis Corporation Method and apparatus for delivery of therapeutic agent
US5062829A (en) 1989-03-17 1991-11-05 Carter Holt Harvey Plastic Products Group Limited Relates to devices for administering a substance such as a drug or chemical or the like
US5100429A (en) 1989-04-28 1992-03-31 C. R. Bard, Inc. Endovascular stent and delivery system
US4990155A (en) 1989-05-19 1991-02-05 Wilkoff Howard M Surgical stent method and apparatus
US4994071A (en) 1989-05-22 1991-02-19 Cordis Corporation Bifurcating stent apparatus and method
US5061273A (en) 1989-06-01 1991-10-29 Yock Paul G Angioplasty apparatus facilitating rapid exchanges
US5476476A (en) 1989-06-06 1995-12-19 Cordis Corporation Dilatation balloon assembly
US5037392A (en) 1989-06-06 1991-08-06 Cordis Corporation Stent-implanting balloon assembly
US5116318A (en) 1989-06-06 1992-05-26 Cordis Corporation Dilatation balloon within an elastic sleeve
US5171262A (en) 1989-06-15 1992-12-15 Cordis Corporation Non-woven endoprosthesis
US5015253A (en) 1989-06-15 1991-05-14 Cordis Corporation Non-woven endoprosthesis
US5242397A (en) 1989-06-20 1993-09-07 Cedars-Sinai Medical Center Catheter device and method of use for intramural delivery of protein kinase C and tyrosine protein kinase inhibitors to prevent restenosis after balloon angioplasty
EP0407951A3 (en) 1989-07-10 1992-03-04 Shipley Company Inc. Method for applying a photoresist to a 3-d conductive substrate
US5084065A (en) 1989-07-10 1992-01-28 Corvita Corporation Reinforced graft assembly
US5026377A (en) 1989-07-13 1991-06-25 American Medical Systems, Inc. Stent placement instrument and method
EP0408245A1 (en) 1989-07-13 1991-01-16 American Medical Systems, Inc. Stent placement instrument
US5292331A (en) 1989-08-24 1994-03-08 Applied Vascular Engineering, Inc. Endovascular support device
US5034001A (en) 1989-09-08 1991-07-23 Advanced Cardiovascular Systems, Inc. Method of repairing a damaged blood vessel with an expandable cage catheter
US5180368A (en) 1989-09-08 1993-01-19 Advanced Cardiovascular Systems, Inc. Rapidly exchangeable and expandable cage catheter for repairing damaged blood vessels
US5002560A (en) 1989-09-08 1991-03-26 Advanced Cardiovascular Systems, Inc. Expandable cage catheter with a rotatable guide
EP0421729A2 (en) 1989-10-02 1991-04-10 Medtronic, Inc. Articulated stent
US5104404A (en) 1989-10-02 1992-04-14 Medtronic, Inc. Articulated stent
EP0423916A1 (en) 1989-10-17 1991-04-24 Cook Incorporated Percutaneous stent
US5035706A (en) 1989-10-17 1991-07-30 Cook Incorporated Percutaneous stent and method for retrieval thereof
EP0428479A1 (en) 1989-11-01 1991-05-22 Schneider (Europe) Ag Stent and catheter for inserting the stent
WO1991007139A1 (en) 1989-11-09 1991-05-30 Ian Leonard Producing prostheses
US5089006A (en) 1989-11-29 1992-02-18 Stiles Frank B Biological duct liner and installation catheter
US5234456A (en) 1990-02-08 1993-08-10 Pfizer Hospital Products Group, Inc. Hydrophilic stent
US5108416A (en) 1990-02-13 1992-04-28 C. R. Bard, Inc. Stent introducer system
US5997468A (en) 1990-02-28 1999-12-07 Medtronic, Inc. Intraluminal drug eluting prosthesis method
US5378239A (en) 1990-04-12 1995-01-03 Schneider (Usa) Inc. Radially expandable fixation member constructed of recovery metal
US5071407A (en) 1990-04-12 1991-12-10 Schneider (U.S.A.) Inc. Radially expandable fixation member
US5158548A (en) 1990-04-25 1992-10-27 Advanced Cardiovascular Systems, Inc. Method and system for stent delivery
US5242399A (en) 1990-04-25 1993-09-07 Advanced Cardiovascular Systems, Inc. Method and system for stent delivery
US5344426A (en) 1990-04-25 1994-09-06 Advanced Cardiovascular Systems, Inc. Method and system for stent delivery
US5123917A (en) 1990-04-27 1992-06-23 Lee Peter Y Expandable intraluminal vascular graft
US5078736A (en) 1990-05-04 1992-01-07 Interventional Thermodynamics, Inc. Method and apparatus for maintaining patency in the body passages
US5064435A (en) 1990-06-28 1991-11-12 Schneider (Usa) Inc. Self-expanding prosthesis having stable axial length
US5122154A (en) 1990-08-15 1992-06-16 Rhodes Valentine J Endovascular bypass graft
US5217482A (en) 1990-08-28 1993-06-08 Scimed Life Systems, Inc. Balloon catheter with distal guide wire lumen
US5163952A (en) 1990-09-14 1992-11-17 Michael Froix Expandable polymeric stent with memory and delivery apparatus and method
US5344425A (en) 1990-09-14 1994-09-06 Interface Biomedical Laboratories, Corp. Intravascular stent and method for conditioning the surfaces thereof
US5108417A (en) 1990-09-14 1992-04-28 Interface Biomedical Laboratories Corp. Anti-turbulent, anti-thrombogenic intravascular stent
US5282824A (en) 1990-10-09 1994-02-01 Cook, Incorporated Percutaneous stent assembly
US5222971A (en) 1990-10-09 1993-06-29 Scimed Life Systems, Inc. Temporary stent and methods for use and manufacture
WO1992006734A1 (en) 1990-10-18 1992-04-30 Ho Young Song Self-expanding endovascular stent
US5330500A (en) 1990-10-18 1994-07-19 Song Ho Y Self-expanding endovascular stent with silicone coating
WO1992009246A1 (en) 1990-11-28 1992-06-11 Numed, Inc. Intravascular radially expandable stent and method
US5161547A (en) 1990-11-28 1992-11-10 Numed, Inc. Method of forming an intravascular radially expandable stent
US5116360A (en) 1990-12-27 1992-05-26 Corvita Corporation Mesh composite graft
US5163951A (en) 1990-12-27 1992-11-17 Corvita Corporation Mesh composite graft
US5413597A (en) 1990-12-29 1995-05-09 Krajicek; Milan Three-layer vascular prostheses
US5782855A (en) 1991-01-28 1998-07-21 Advanced Cardiovascular Systems, Inc. Stent delivery system
US5507768A (en) 1991-01-28 1996-04-16 Advanced Cardiovascular Systems, Inc. Stent delivery system
US5135536A (en) 1991-02-05 1992-08-04 Cordis Corporation Endovascular stent and method
US5073694A (en) 1991-02-21 1991-12-17 Synthes (U.S.A.) Method and apparatus for laser cutting a hollow metal workpiece
US5116365A (en) 1991-02-22 1992-05-26 Cordis Corporation Stent apparatus and method for making
US5197978B1 (en) 1991-04-26 1996-05-28 Advanced Coronary Tech Removable heat-recoverable tissue supporting device
US5197978A (en) 1991-04-26 1993-03-30 Advanced Coronary Technology, Inc. Removable heat-recoverable tissue supporting device
US5304200A (en) 1991-05-29 1994-04-19 Cordis Corporation Welded radially expandable endoprosthesis and the like
EP0517075A1 (en) 1991-06-06 1992-12-09 Advanced Cardiovascular Systems, Inc. Intravascular catheter with a nontraumatic distal tip
FR2677872A1 (en) 1991-06-19 1992-12-24 Celsa Lg Device for assisting in the positioning of a filter for trapping thrombi
US5356433A (en) 1991-08-13 1994-10-18 Cordis Corporation Biocompatible metal surfaces
US5183085A (en) 1991-09-27 1993-02-02 Hans Timmermans Method and apparatus for compressing a stent prior to insertion
US5314472A (en) 1991-10-01 1994-05-24 Cook Incorporated Vascular stent
US5290305A (en) 1991-10-11 1994-03-01 Kanji Inoue Appliance collapsible for insertion into human organs and capable of resilient restoration
US5242452A (en) 1991-10-11 1993-09-07 Kanji Inoue Device for collapsing an appliance collapsible for insertion into human organs
US5421955A (en) 1991-10-28 1995-06-06 Advanced Cardiovascular Systems, Inc. Expandable stents and method for making same
US5514154A (en) 1991-10-28 1996-05-07 Advanced Cardiovascular Systems, Inc. Expandable stents
US5603721A (en) 1991-10-28 1997-02-18 Advanced Cardiovascular Systems, Inc. Expandable stents and method for making same
US6066168A (en) 1991-10-28 2000-05-23 Advanced Cardiovascular Systems, Inc. Expandable stents and method for making same
EP0540290A2 (en) 1991-10-28 1993-05-05 Advanced Cardiovascular Systems, Inc. Expandable stents and method for making same
US5421955B1 (en) 1991-10-28 1998-01-20 Advanced Cardiovascular System Expandable stents and method for making same
US5372600A (en) 1991-10-31 1994-12-13 Instent Inc. Stent delivery systems
EP0541443A1 (en) 1991-11-08 1993-05-12 Meadox Medicals, Inc. Endoprosthesis for transluminal implantation
US5383892A (en) 1991-11-08 1995-01-24 Meadox France Stent for transluminal implantation
US5192297A (en) 1991-12-31 1993-03-09 Medtronic, Inc. Apparatus and method for placement and implantation of a stent
US5484449A (en) 1992-01-07 1996-01-16 Medtronic, Inc. Temporary support for a body lumen and method
US5423885A (en) 1992-01-31 1995-06-13 Advanced Cardiovascular Systems, Inc. Stent capable of attachment within a body lumen
US5282823A (en) 1992-03-19 1994-02-01 Medtronic, Inc. Intravascular radially expandable stent
US5368566A (en) 1992-04-29 1994-11-29 Cardiovascular Dynamics, Inc. Delivery and temporary stent catheter having a reinforced perfusion lumen
US5354308A (en) 1992-05-01 1994-10-11 Beth Israel Hospital Association Metal wire stent
US5395390A (en) 1992-05-01 1995-03-07 The Beth Israel Hospital Association Metal wire stent
US5746765A (en) 1992-05-01 1998-05-05 Nitinol Medical Technologies, Inc. Stent and method and apparatus for forming and delivering the same
US5405378A (en) 1992-05-20 1995-04-11 Strecker; Ernst P. Device with a prosthesis implantable in the body of a patient
US5290295A (en) 1992-07-15 1994-03-01 Querals & Fine, Inc. Insertion tool for an intraluminal graft procedure
US5653690A (en) 1992-12-30 1997-08-05 Medtronic, Inc. Catheter having a balloon with retention enhancement
US5720726A (en) 1992-12-30 1998-02-24 Medtronic, Inc. Balloon catheter having retention enhancements on the balloon
EP0606165A1 (en) 1993-01-06 1994-07-13 Ethicon Inc. Stent
WO1994017754A1 (en) 1993-02-04 1994-08-18 Angiomed Ag Stent
US5360401A (en) 1993-02-18 1994-11-01 Advanced Cardiovascular Systems, Inc. Catheter for stent delivery
US5984964A (en) 1993-04-13 1999-11-16 Boston Scientific Corporation Prothesis delivery system
US5458615A (en) 1993-07-06 1995-10-17 Advanced Cardiovascular Systems, Inc. Stent delivery system
US5716396A (en) 1993-09-16 1998-02-10 Cordis Corporation Endoprosthesis having multiple laser welded junctions method and procedure
US5571135A (en) 1993-10-22 1996-11-05 Scimed Life Systems Inc. Stent delivery apparatus and method
US5445646A (en) 1993-10-22 1995-08-29 Scimed Lifesystems, Inc. Single layer hydraulic sheath stent delivery apparatus and method
US5733325A (en) 1993-11-04 1998-03-31 C. R. Bard, Inc. Non-migrating vascular prosthesis and minimally invasive placement system
US5545132A (en) 1993-12-21 1996-08-13 C. R. Bard, Inc. Helically grooved balloon for dilatation catheter and method of using
US5569295A (en) 1993-12-28 1996-10-29 Advanced Cardiovascular Systems, Inc. Expandable stents and method for making same
US5476506A (en) 1994-02-08 1995-12-19 Ethicon, Inc. Bi-directional crimped graft
WO1995023563A1 (en) 1994-03-04 1995-09-08 Universite De Montreal Endovascular hepatic prostheses
US5980552A (en) 1994-03-17 1999-11-09 Medinol Ltd. Articulated stent
US5449373A (en) 1994-03-17 1995-09-12 Medinol Ltd. Articulated stent
US5733303A (en) 1994-03-17 1998-03-31 Medinol Ltd. Flexible expandable stent
WO1995026695A2 (en) 1994-04-01 1995-10-12 Prograft Medical, Inc. Self-expandable stent and stent-graft and method of using them
US5456694A (en) 1994-05-13 1995-10-10 Stentco, Inc. Device for delivering and deploying intraluminal devices
US5716393A (en) 1994-05-26 1998-02-10 Angiomed Gmbh & Co. Medizintechnik Kg Stent with an end of greater diameter than its main body
EP0688545A1 (en) 1994-06-17 1995-12-27 Terumo Kabushiki Kaisha Indwelling stent and the method for manufacturing the same
US5527324A (en) 1994-09-07 1996-06-18 Krantz; Kermit E. Surgical stent
WO1996009013A1 (en) 1994-09-21 1996-03-28 Wake Forest University Expandable, intraluminal stents
US5817152A (en) 1994-10-19 1998-10-06 Birdsall; Matthew Connected stent apparatus
US5836965A (en) 1994-10-19 1998-11-17 Jendersee; Brad Stent delivery and deployment method
US5906640A (en) 1994-11-03 1999-05-25 Divysio Solutions Ulc Bifurcated stent and method for the manufacture and delivery of same
US5800521A (en) 1994-11-09 1998-09-01 Endotex Interventional Systems, Inc. Prosthetic graft and method for aneurysm repair
WO1996026689A1 (en) 1995-03-01 1996-09-06 Scimed Life Systems, Inc. Improved longitudinally flexible expandable stent
US5800526A (en) 1995-03-17 1998-09-01 Endotex Interventional Systems, Inc. Multi-anchor stent
US5693089A (en) 1995-04-12 1997-12-02 Inoue; Kanji Method of collapsing an implantable appliance
US6010530A (en) 1995-06-07 2000-01-04 Boston Scientific Technology, Inc. Self-expanding endoluminal prosthesis
DE19537872A1 (en) 1995-10-11 1997-04-17 Eckhard Prof Dr Alt Expandable support for blood vessels
US5776161A (en) 1995-10-16 1998-07-07 Instent, Inc. Medical stents, apparatus and method for making same
US6287336B1 (en) 1995-10-16 2001-09-11 Medtronic, Inc. Variable flexibility stent
US5626604A (en) 1995-12-05 1997-05-06 Cordis Corporation Hand held stent crimping device
US5810868A (en) 1995-12-07 1998-09-22 Arterial Vascular Engineering, Inc. Stent for improved transluminal deployment
US6217608B1 (en) 1996-03-05 2001-04-17 Divysio Solutions Ulc Expandable stent and method for delivery of same
US6183506B1 (en) 1996-03-05 2001-02-06 Divysio Solutions Ltd. Expandable stent and method for delivery of same
US6200337B1 (en) 1996-03-10 2001-03-13 Terumo Kabushiki Kaisha Implanting stent
US6071298A (en) 1996-03-22 2000-06-06 Arterial Vascular Engineering Inc. Stents for supporting lumens in living tissue
US5861027A (en) 1996-04-10 1999-01-19 Variomed Ag Stent for the transluminal implantation in hollow organs
EP0800801A1 (en) 1996-04-10 1997-10-15 Advanced Cardiovascular Systems, Inc. Stent having varied amounts of structural strength along its length
US5653691A (en) 1996-04-25 1997-08-05 Rupp; Garry Eugene Thickened inner lumen for uniform stent expansion and method of making
US5922021A (en) 1996-04-26 1999-07-13 Jang; G. David Intravascular stent
US5954743A (en) 1996-04-26 1999-09-21 Jang; G. David Intravascular stent
US5830217A (en) 1996-08-09 1998-11-03 Thomas J. Fogarty Soluble fixation device and method for stent delivery catheters
US6881216B2 (en) 1996-08-23 2005-04-19 Boston Scientific Scimed, Inc. Balloon catheter with stent securement means
WO1998022159A2 (en) 1996-11-07 1998-05-28 Medtronic Instent Inc. Variable flexibility stent
US5925061A (en) 1997-01-13 1999-07-20 Gore Enterprise Holdings, Inc. Low profile vascular stent
US5911452A (en) * 1997-02-04 1999-06-15 Advanced Cardiovascular Systems, Inc. Apparatus and method for mounting a stent onto a catheter
US5827321A (en) 1997-02-07 1998-10-27 Cornerstone Devices, Inc. Non-Foreshortening intraluminal prosthesis
US6106548A (en) 1997-02-07 2000-08-22 Endosystems Llc Non-foreshortening intraluminal prosthesis
WO1998048734A1 (en) 1997-04-25 1998-11-05 Jang G David Intravascular stent
US5810871A (en) 1997-04-29 1998-09-22 Medtronic, Inc. Stent delivery system
US5741327A (en) 1997-05-06 1998-04-21 Global Therapeutics, Inc. Surgical stent featuring radiopaque markers
US6344055B1 (en) 1997-05-14 2002-02-05 Novo Rps Ulc Method for production of an expandable stent
US6048361A (en) 1997-05-17 2000-04-11 Jomed Implantate Gmbh Balloon catheter and multi-guidewire stent for implanting in the region of branched vessels
US6017365A (en) 1997-05-20 2000-01-25 Jomed Implantate Gmbh Coronary stent
US5836966A (en) 1997-05-22 1998-11-17 Scimed Life Systems, Inc. Variable expansion force stent
US6146403A (en) 1997-05-22 2000-11-14 Scimed Life Systems, Inc. Variable expansion force stent
WO1999002105A1 (en) 1997-07-08 1999-01-21 Novo Rps Ulc Expandable stent
US5855600A (en) 1997-08-01 1999-01-05 Inflow Dynamics Inc. Flexible implantable stent with composite design
US6059822A (en) 1997-08-22 2000-05-09 Uni-Cath Inc. Stent with different mesh patterns
US6206910B1 (en) 1997-09-11 2001-03-27 Wake Forest University Compliant intraluminal stents
US6231598B1 (en) 1997-09-24 2001-05-15 Med Institute, Inc. Radially expandable stent
US5948016A (en) 1997-09-25 1999-09-07 Jang; G. David Intravascular stent with non-parallel slots
US6042606A (en) 1997-09-29 2000-03-28 Cook Incorporated Radially expandable non-axially contracting surgical stent
US6071308A (en) 1997-10-01 2000-06-06 Boston Scientific Corporation Flexible metal wire stent
EP0916318A1 (en) 1997-10-16 1999-05-19 SciMed Life Systems, Inc. Stent crimper
US6033435A (en) 1997-11-03 2000-03-07 Divysio Solutions Ulc Bifurcated stent and method for the manufacture and delivery of same
US6179867B1 (en) 1998-01-16 2001-01-30 Advanced Cardiovascular Systems, Inc. Flexible stent and method of use
US5938697A (en) 1998-03-04 1999-08-17 Scimed Life Systems, Inc. Stent having variable properties
US6159238A (en) 1998-03-04 2000-12-12 Scimed Life Systems, Inc Stent having variable properties and method of its use
US6063092A (en) * 1998-04-07 2000-05-16 Medtronic Inc. Heat set and crimping process to optimize stent retention
US5931851A (en) 1998-04-21 1999-08-03 Advanced Cardiovascular Systems, Inc. Method and apparatus for rubber-tube crimping tool with premount stent
US5911754A (en) 1998-07-24 1999-06-15 Uni-Cath Inc. Flexible stent with effective strut and connector patterns
US7004966B2 (en) 1998-09-30 2006-02-28 C. R. Bard, Inc. Selective adherence of stent-graft coverings
US6042597A (en) 1998-10-23 2000-03-28 Scimed Life Systems, Inc. Helical stent design
US6293959B1 (en) * 1998-11-16 2001-09-25 Cordis Corporation Balloon catheter and stent delivery system having enhanced stent retention and method
US6340366B2 (en) 1998-12-08 2002-01-22 Bandula Wijay Stent with nested or overlapping rings
US6273910B1 (en) 1999-03-11 2001-08-14 Advanced Cardiovascular Systems, Inc. Stent with varying strut geometry
US7056323B2 (en) 1999-03-31 2006-06-06 Scimed Life Systems, Inc. Stent security balloon/balloon catheter
US6273911B1 (en) 1999-04-22 2001-08-14 Advanced Cardiovascular Systems, Inc. Variable strength stent
US6273901B1 (en) 1999-08-10 2001-08-14 Scimed Life Systems, Inc. Thrombosis filter having a surface treatment
US6915560B2 (en) 1999-09-22 2005-07-12 Boston Scientific Scimed, Inc. Apparatus for contracting, loading or crimping self-expanding and balloon expandable stent devices
US6823576B2 (en) 1999-09-22 2004-11-30 Scimed Life Systems, Inc. Method and apparatus for contracting, loading or crimping self-expanding and balloon expandable stent devices
US7060218B2 (en) 2001-03-06 2006-06-13 Advanced Cardiovascular Systems, Inc. Adjustable length mold assemblies
US20040177805A1 (en) 2001-03-29 2004-09-16 Luuk Hijlkema Thermal regulation of a coated work-piece during the reconfiguration of the coated work-piece
EP1295570B1 (en) 2001-09-19 2007-11-21 Abbott Laboratories Vascular Enterprises Limited Cold-molding process for loading a stent onto a stent delivery system
US6863683B2 (en) 2001-09-19 2005-03-08 Abbott Laboratoris Vascular Entities Limited Cold-molding process for loading a stent onto a stent delivery system
US20030204238A1 (en) 2002-04-26 2003-10-30 Eugene Tedeschi Coated stent with crimpable coating
US20030208254A1 (en) 2002-05-03 2003-11-06 James Shortt Method and apparatus for mounting a stent onto a stent delivery system
US20060100694A1 (en) 2002-06-13 2006-05-11 Oren Globerman Guidewire system
US6955658B2 (en) 2003-01-23 2005-10-18 Medtronic Vascular, Inc. Mold for forming a medical balloon
WO2005053937A1 (en) 2003-12-01 2005-06-16 Advanced Cardiovascular Systems, Inc. Temperature controlled crimping
US7021114B2 (en) 2004-04-16 2006-04-04 Boston Scientific Scimed, Inc. Stent crimper
WO2006110861A8 (en) 2005-04-12 2007-05-03 Advanced Cardiovascular System Method of stent mounting to form a balloon catheter having improved retention of a drug delivery stent

Non-Patent Citations (18)

* Cited by examiner, † Cited by third party
Title
70th Scientific Assembly and Annual Meeting: Scientific Program, Radiology, Washington, D.C., Nov. 25-30, 1984, Special Edition, vol. 153(P).
72nd Scientific Assembly and Annual Meeting: RSNA Scientific Program, Radiology, Chicago: Nov. 30-Dec. 5, 1986. Special Edition, vol. 161(P).
C.R. Bard. PE Plus Peripheral Balloon Dilatation Catheter, C.R. Bard, Inc., Aug. 1985.
Charnsangavej, C., M.D., et al., Endovascular Stent for Use in Aortic Dissension: An In Vitro Experiment, Radiology, pp. 323-324, vol. 157, No. 2, Nov. 1985.
Charnsangavej, C., M.D.. et al., Stenosis of The Vena Cava: Preliminary Assessment of Treatment With Expandable Metallic Stents, Radiology, pp. 295-298, vol. 161, Nov. 1986.
Cragg, et al., Non-Surgical Placement of Arterial Endoprostheses: A New Technique Using Nitinol Wire, Radiology Journal, pp. 261-163, Apr. 1983.
Dotter, Charles T. Transluminal Expandable Nitinol Coil Stent Grafting: Preliminary Report, Radiology Journal, pp. 259-260, Apr. 1983.
Dotter, Charles T., Transluminally Placed Coilspring Endarterial Tube Grafts. Investigative Radiology, pp. 329-332, Sep./Oct. 1969.
Duprat, et al., Flexible Balloon-Expanded Stent for Small Vessels, Radiology Journal, pp. 276-178, 1987.
Furui, S. M.D., et al., Hepatic Inferior Vena Cava Obstruction: Treatment of Two Types with Gianturco Expandable Metallic Stents. Radiology, pp. 665-670. vol. 176, No. 3, Sep. 1990.
Maass, et al., Radiological follow-Up of Transluminally Inserted Vascular Endoprostheses: An Experimental Study Using Expanding Spirals. Radiology Journal, pp. 659-663, 1984.
Palmaz, et al., Expandable Intraluminal Graft: A Preliminary Study, Radiology Journal, pp. 73-77, 1985.
Program: Day 2 (Nov. 18) The Radiological Society of North America, Radiology, Chicago: Nov. 30-Dec. 5. 1986. Special Edition. vol. I 61(P).
Rösch, J., M.D., et al., Gianturco Expandable Stents in Experimental and Clinical Use, paper presented at The Twelfth Annual Course on "Diagnostic angiography and Interventional Radiology" Mar. 23-26, 1987 (Pittsburgh, Pennsylvania).
Rösch, J., M.D., et al., TransjugularIntrahepatic Portacaval Shunt: An Experimental Work. The American Journal of Surgery, pp. 588-592, vol. 121, May 1971.
Rösch, J., M.D.. et al., Experimental Intrahepatic Portacaval anastomosis: Use of Expandable Gianturco Stents, Radiology, pp. 481-485, vol. 162, Feb. 1987.
Wallace, Michael J., et al., Tracheobronchial Tree: Expandable Metallic Stents Used in Experimental and Clinical Applications (Work in Progress), Radiology, pp. 309-312, vol. 158, Feb. 1986.
Wright, et al., Percutaneous Endovascular Stents: An Experimental Evaluation, Radiology Journal, pp. 69-72, 1985.

Cited By (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9295570B2 (en) 2001-09-19 2016-03-29 Abbott Laboratories Vascular Enterprises Limited Cold-molding process for loading a stent onto a stent delivery system
US8540927B2 (en) * 2005-04-12 2013-09-24 Abbott Cardiovascular Systems Inc. Method for retaining a vascular stent on a catheter
US9259341B2 (en) 2006-06-19 2016-02-16 Abbott Cardiovascular Systems Inc. Methods for improving stent retention on a balloon catheter
US9579225B2 (en) 2006-06-19 2017-02-28 Abbott Cardiovascular Systems Inc. Methods for improving stent retention on a balloon catheter
EP3009109A1 (en) 2010-09-30 2016-04-20 Abbott Cardiovascular Systems Inc. Stent crimping method
US8595913B2 (en) * 2010-09-30 2013-12-03 Advanced Cardiovascular Systems, Inc. Stent crimping methods
US9308106B2 (en) 2010-09-30 2016-04-12 Abbott Cardiovascular Systems Inc. Stent crimping methods
WO2012044454A1 (en) 2010-09-30 2012-04-05 Abbott Cardiovascular Systems Inc. Stent crimping methods
US20120079706A1 (en) * 2010-09-30 2012-04-05 Advanced Cardiovascular Systems, Inc. Stent Crimping Methods
US20130296997A1 (en) * 2011-08-30 2013-11-07 Suraj Govind Kamat Deployment of Stents within Bifurcated Vessels
US8574283B1 (en) * 2011-08-30 2013-11-05 Suraj Govind Kamat Deployment of stents within bifurcated vessels
US20160096308A1 (en) * 2014-10-02 2016-04-07 Inspiremd, Ltd Stent thermoforming apparatus and methods
US9527234B2 (en) * 2014-10-02 2016-12-27 Inspiremd, Ltd. Stent thermoforming apparatus and methods
US9782278B2 (en) 2014-10-02 2017-10-10 Inspiremd, Ltd. Stent thermoforming apparatus and methods

Also Published As

Publication number Publication date Type
EP2029052B1 (en) 2014-05-07 grant
EP2029052A2 (en) 2009-03-04 application
EP3207903A1 (en) 2017-08-23 application
EP2752171B1 (en) 2017-05-03 grant
WO2007146543A2 (en) 2007-12-21 application
JP2009539560A (en) 2009-11-19 application
WO2007146543A3 (en) 2008-01-31 application
JP5184524B2 (en) 2013-04-17 grant
EP2752171A2 (en) 2014-07-09 application
US20070204455A1 (en) 2007-09-06 application
US20100278956A1 (en) 2010-11-04 application
EP2752171A3 (en) 2014-07-30 application

Similar Documents

Publication Publication Date Title
US5972016A (en) Stent crimping device and method of use
US6620191B1 (en) System for releasably securing a stent on a catheter assembly and method of use
US6736841B2 (en) Textured and/or marked balloon for stent delivery
US7056323B2 (en) Stent security balloon/balloon catheter
US6709440B2 (en) Stent and catheter assembly and method for treating bifurcations
US6620128B1 (en) Balloon blowing process with metered volumetric inflation
US20060076708A1 (en) Method of fabricating a biaxially oriented implantable medical device
US6221042B1 (en) Balloon with reversed cones
US20040088038A1 (en) Porous metal for drug-loaded stents
US6036697A (en) Balloon catheter with balloon inflation at distal end of balloon
US5415635A (en) Balloon assembly with separately inflatable sections
US5672169A (en) Stent mounting device
US20030181973A1 (en) Reduced restenosis drug containing stents
US5645560A (en) Fixed focal balloon for interactive angioplasty and stent implantation
US5522882A (en) Method and apparatus for balloon expandable stent-graft delivery
US20040122465A1 (en) Balloon catheter having an external guidewire
US6837870B2 (en) Catheter having a multilayered shaft section with a reinforcing mandrel
US5653691A (en) Thickened inner lumen for uniform stent expansion and method of making
US5693066A (en) Stent mounting and transfer device and method
US6287314B1 (en) Stent deploying catheter system
US8052638B2 (en) Robust multi-layer balloon
US20030033001A1 (en) Stent holding member and stent feeding system
US7105013B2 (en) Protective sleeve assembly for a balloon catheter
US20080262470A1 (en) Catheter having a readily bondable multilayer soft tip
US20060136032A1 (en) Balloon catheter having a balloon with hybrid porosity sublayers

Legal Events

Date Code Title Description
AS Assignment

Owner name: ADVANCED CARDIOVASCULAR SYSTEMS, INC., CALIFORNIA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:KNOTT, BOYD V.;MCNIVEN, SEAN;STIGALL, JEREMY;REEL/FRAME:017985/0574

Effective date: 20060609

AS Assignment

Owner name: ABBOTT CARDIOVASCULAR SYSTEMS INC., CALIFORNIA

Free format text: CHANGE OF NAME;ASSIGNOR:ADVANCED CARDIOVASCULAR SYSTEMS, INC.;REEL/FRAME:019178/0915

Effective date: 20070209

FPAY Fee payment

Year of fee payment: 4

MAFP

Free format text: PAYMENT OF MAINTENANCE FEE, 8TH YEAR, LARGE ENTITY (ORIGINAL EVENT CODE: M1552)

Year of fee payment: 8